Microfabricated neurostimulation device

ABSTRACT

Described herein are microelectrode array devices, and methods of fabrication and use of the same, to provide highly localized and efficient electrical stimulation of a neurological target. The device includes multiple microelectrode elements arranged along an elongated probe shaft. The microelectrode elements are dimensioned and shaped so as to target individual neurons, groups of neurons, and neural tissue as may be located in an animal nervous system, such as deep within a human brain. Beneficially, the neurological probe can be used to facilitate location of the neurological target and remain implanted for long-term monitoring and/or stimulation.

RELATED APPLICATIONS

This is a continuing patent application, which claims priority to U.S.patent application Ser. No. 15/185,709, filed Jun. 16, 2016 and nowissued as U.S. Pat. No. 10,406,350, which claims priority to U.S. patentapplication Ser. No. 14/309,491, filed Jun. 19, 2014, and now issued asU.S. Pat. No. 9,440,082, which is a continuing patent application ofU.S. patent application Ser. No. 13/128,821, filed Aug. 1, 2011, and nowissued as U.S. Pat. No. 8,788,064, which is the U.S. National Stage ofPCT International Application Number PCT/IB2009/007715, filed Nov. 12,2009, which claims priority to U.S. Provisional Application No.61/113,912, filed Nov. 12, 2008. The contents of the foregoingapplications are incorporated herein by reference in their entireties.

FIELD

The present invention relates generally to the field of interacting withbiological tissue through the use of electrical probes, and moreparticularly to interacting with a neurological target through the useof microelectrode probes.

BACKGROUND

Neurostimulation is a category of medical devices that are used totransfer electric charge or electrical fields to tissue and result in aphysiological change which benefits the patient, or performs aphysiological measurement. Neurostimulation is used today in thecochlea, the retina, the peripheral nerve system, the spine, the brainand other parts of the body.

In a particular application of Neurostimulation, conductive electrodesare placed in contact with certain deep brain structures in order totreat certain neurological conditions. In the case of stimulating theSubthalamic Nucleus, for example, as described in U.S. Pat. No.5,716,377, or the Globus Pallidus, for example, as described in U.S.Pat. No. 5,683,422, the therapy can treat the symptoms of MovementDisorders such as Parkinson's disease, Essential Tremor or Dystonia. Inthe case of stimulating the cerebellum, Hippocampus and other brainstructures, the therapy can treat the symptoms of Epilepsy [Theodore, W.H., Fisher, R. S., “Brain stimulation for epilepsy”, Lancet Neurology, 3(2), pp. 111-118, (2004).].

An implantable pulse generator supplies the electrical signal to theelectrode lead in contact with the brain structure. All components areplaced surgically.

In most prior art the electrode placed in contact with the brain tissuehas been metallic, cylindrical, and relatively large in size (e.g., 1.5mm in length). In many cases, the electrodes are as large as the brainstructures themselves. The large size of electrodes prevents specificand precise stimulation of small brain targets such as thepedunculopontine nucleus. The resulting large electric fields andassociated current paths stimulate other structures of the brain, and donot concentrate on the intended target. Furthermore, these largeelectrodes cannot be used to identify the targets of the brain byneural-recording because the area they cover is very large.

Current techniques that determine placement of such relatively largeelectrodes are accomplished cutaneously by first inserting a relativelysmall (e.g., 600 μm diameter probe). The relatively small probe can beinserted along an approach near the target. Recordings of neuralactivity can be made as the probe is advanced along the approach untilthe intended target is located. The depth of the probe from a referenceis recorded and the relatively large electrodes are inserted along thesame trajectory, being placed at the recorded depth. This process iscomplex, requiring a highly skilled surgeon to place both the probe andlater the electrode. Repositioning and removal of the probe andreinsertion of the electrode subject the patient to heightened risk asthe risk of tissue damage and bleeding is increased.

Attempts have been made at developing microfabricated devicesspecifically designed to incorporate an array of microelectrodes whichcan stimulate small volumes of tissue in the deep brain, for example, asdescribed in U.S. Pat. App. Pub. 2007/0118197, or “MultisiteMicroelectrodes for Use in Human Deep Brain Stimulation” by Hofmann etal., Microtechnologies in Medicine and Biology, 2006 InternationalConference on (2006) Pgs. 284-287. The prior devices however do not havea clear path to clinical use because they are too unfamiliar to theneurosurgeon performing the implantation procedure.

An important requirement for a successful outcome of deep brainstimulation (DB S) treatment, is the accurate placement of thestimulation electrodes within the stimulation target area. Mislocationmay result in unwanted side-effects, including sensory motor effects andmood changes. Prior art procedures approximately localize the target bypre-surgical imaging and planning to identify a trajectory to minimizerisk of damage. It may be impossible to locate the exact functionalanatomy within a target region of the brain. The targets themselves maybe only a few mm or less, and not detectable through standard imagingtechniques alone. Also, position changes of the brain may occur whensurgically opening the skull to implant the electrodes and wheninserting the electrodes. Current procedures insert test electrodes usedto perform electrophysiological exploration of the target area. Once theprecise target area is located, the chronic stimulation electrodes canbe implanted at the precise location.

Disadvantages to the current technology include extension of operationtime by several hours, which can be an increased burden for the patient,who is typically awake during such procedures, and extended costassociated with lengthier procedures. Increased risk of surgicalcomplications from bleeding or tissue damage caused by repeatedinsertion and extraction of test and chronic leads. Possibility thatchronic leads are not precisely located at identified target for anynumber of reasons, including further brain movement. An increased chanceof infection due to an open craniotomy for several hours.

SUMMARY

For efficient stimulation of small brain structures, small electrodesare required. After placement of the electrode lead, the surgeon shouldbe able to identify the area of the brain that requires stimulation byrecording from the electrode. Subsequently the surgeon should stimulatethe identified structure.

For efficient stimulation of large brain structures, electrodes thatcontain a higher number of edges are provided.

The invention describes a system which places many microelectrodestructures in the brain, and allows the surgeon to apply a signal toeach microelectrode separately, or in parallel. Furthermore, usingelectronics to record neural activity from the system, the surgeon candevelop a localized map of neural activity in the region which theelectrode is implanted.

In one aspect, the invention relates to an implantable neurologicalprobe. The neurological probe includes an elongated probe shaft and anarrangement of multiple microelectrode elements disposed at a distal endof the elongated probe shaft. At least one electrical contact isarranged proximally along the probe shaft. The neurological probe alsoincludes at least one electrical conductor in electrical communicationbetween at least one of the plurality of microelectrode elements and theat least one electrical contact.

In another aspect, the invention relates to a process for stimulating aneurological target. The process includes implanting a neurologicalprobe within a vicinity of a neurological target site. The neurologicalprobe itself comprising an elongated probe shaft, multiplemicroelectrode elements arranged at a distal end of the elongated probeshaft, at least one electrical contact arranged proximally along theprobe shaft, and at least one electrical conductor in electricalcommunication between at least one of the multiple microelectrodeelements and the at least one electrical contact. The at least oneelectrical contact is connected to a neurological stimulation sourcesupplying an electrical signal. One or more of the microelectrodeelements is energized by the supplied electrical signal. The one or moreenergized microelectrode elements produce an electric field adapted tostimulate the neurological target site.

In yet another aspect, the invention relates to an implantableneurological probe kit. The kit includes a neurological probe. Theneurological probe includes an elongated flexible probe shaft having acentral lumen accessible at a proximal end of the neurological probe.The device includes multiple microelectrode elements arranged at adistal end of the elongated probe shaft. At least one electrical contactarranged proximally along the probe shaft. At least one electricalconductor in electrical communication between at least one of theplurality of microelectrode elements and the at least one electricalcontact. The neurological probe kit also includes a trocar, or stylet,configured for removable insertion into the central lumen of theelongated flexible probe shaft, to keep the elongated flexible probeshaft substantially rigid during insertion into biological tissue.

BRIEF DESCRIPTION OF THE DRAWINGS

The foregoing and other objects, features and advantages of theinvention will be apparent from the following more particulardescription of preferred embodiments of the invention, as illustrated inthe accompanying drawings in which like reference characters refer tothe same parts throughout the different views. The drawings are notnecessarily to scale, emphasis instead being placed upon illustratingthe principles of the invention.

FIG. 1 is a perspective view of one embodiment of an elongatedmicroelectrode assembly.

FIG. 2 is a perspective view of a portion of a human anatomyillustrating an exemplary elongated microelectrode assembly implantedtherein.

FIG. 3 is a perspective view of a portion of a human anatomyillustrating an exemplary microelectrode structure positioned at aneurological target.

FIG. 4 is a perspective view of a distal portion of the elongatedmicroelectrode assembly of FIG. 1.

FIG. 5 is an image of an embodiment of a microelectrode arraymicroelectromechanical system (MEMS).

FIG. 6 is an image of one embodiment of a microelectrode arrayintegrally attached to a distal portion of an elongated cylindricalstructure.

FIG. 7A is a planar view of an alternative embodiment of amicroelectrode assembly.

FIG. 7B is a perspective view of a distal portion of a microelectrodearray of FIG. 7A.

FIG. 7C is an image of a microelectrode array film that forms the distalportion of the microelectrode assembly of FIG. 7A.

FIG. 7D is an image demonstrating an assembly procedure of the variouscomponents that form the microelectrode array of FIG. 7A.

FIG. 7E is an image of an assembled distal portion of the microelectrodearray of FIG. 7A.

FIG. 8A is an alternative embodiment of an elongated microelectrodeassembly.

FIG. 8B is a perspective view of a distal portion of the elongatedmicroelectrode assembly of FIG. 8A.

FIG. 9 is a detailed perspective view of a distal portion of anembodiment of a microelectrode array micro-electromechanical system(MEMS).

FIG. 10 is a perspective view of the distal portion of an assemblyincluding the microelectrode array of FIG. 9.

FIG. 11A is a planar view of another embodiment of an elongatedmicroelectrode assembly.

FIG. 11B is a more detailed view of a portion of the elongatedmicroelectrode assembly illustrated in FIG. 11A.

FIG. 11C is a more detailed view of a distal portion of the elongatedmicroelectrode assembly illustrated in FIG. 11A.

FIG. 11D is a perspective view of the microelectrode array of FIG. 11A.

FIG. 12 is a schematic diagram of an exemplary microelectrode arraycircuit.

FIG. 13A is a planar view of an elongated microelectrode assembly.

FIG. 13B is a perspective view of a distal portion of the elongatedmicroelectrode assembly in FIG. 13A.

FIG. 13C is a cutaway view of the distal portion of the elongatedmicroelectrode assembly in FIG. 13A illustrating the interiorcomponents.

FIG. 13D is a planar view of an embodiment of a microelectrode filmassembly for use with the neurological probe of FIG. 13A.

FIG. 14A is a perspective view of a distal portion of another embodimentof an elongated microelectrode assembly.

FIG. 14B is a perspective view of a distal portion of yet anotherembodiment of an elongated microelectrode assembly.

FIG. 15A through FIG. 15J illustrate various alternative embodiments ofa pre-installed microelectrode assembly.

FIG. 16A through 16D are cutaway views demonstrating alternativeassembly methods of a distal portion of an embodiment of amicroelectrode array.

FIG. 17A through 17B are cutaway views demonstrating alternativeassembly methods of a distal portion of an embodiment of amicroelectrode array.

FIG. 18A is a more detailed view of a distal portion of an elongatedmicroelectrode assembly.

FIG. 18B is a more detailed cross-sectional view of the distal portionof the elongated microelectrode assembly illustrated in FIG. 18A.

FIG. 18C is a more detailed cross-sectional view of an alternativeassembly of the proximal portion of an elongated microelectrodeassembly.

FIG. 19 is a schematic view of a cross-sectional of a portion of a humananatomy illustrating an exemplary microelectrode structure positioned ata neurological target.

FIG. 20 is a schematic diagram of one embodiment of an electrode tipassembly.

FIG. 21 is a schematic diagram of a distal portion of another embodimentof an microelectrode tip assembly.

FIG. 22A is a perspective view of one embodiment of an elongatedmicroelectrode assembly having a microelectrode tip assembly at a distalend.

FIG. 22B is a more detailed view of a distal end of the elongatedmicroelectrode assembly of FIG. 22A.

FIG. 22C is another more detailed view of the distal end of theelongated microelectrode assembly of FIG. 22A.

FIG. 23 is a perspective view of a distal end of another embodiment ofan elongated microelectrode assembly having an electrode tip assembly ata distal end.

FIG. 24 is a micrograph of a distal portion of an embodiment of amicroelectrode tip.

FIG. 25 is a micrograph of the distal portion of the microelectrode tipillustrated in FIG. 24.

FIG. 26 is a micrograph of a distal portion of another embodiment of amicroelectrode tip.

FIG. 27 is a micrograph of conductive elements of an embodiment of amicroelectrode array.

FIG. 28A is a micrograph of a distal portion of another embodiment of amicroelectrode tip.

FIG. 28B is a micrograph of opposing sides of a distal portion of anembodiment of a microelectrode tip.

FIG. 29A through FIG. 29M illustrate cross sections of an exemplarymicroelectrode device at various different stages of constructionaccording to an exemplary fabrication procedure.

FIG. 30 is a micrograph of an embodiment of a microelectrode.

FIG. 31A is a planar view of a construction element of an embodiment ofa microelectrode tip.

FIG. 31B is a schematic view of a portion of the construction elementillustrated in FIG. 31A.

FIG. 31C is an exploded schematic view of a construction element of anembodiment of a microelectrode tip.

FIG. 31D is a schematic view of another portion of the constructionelement illustrated in FIG. 31B.

FIG. 32A is a perspective view of a distal portion of a microelectrodetip.

FIG. 32B is a cross sectional view of the distal portion of themicroelectrode tip illustrated in FIG. 32A.

FIG. 33 is a functional block diagram of an exemplary embodiment of aneurological microelectrode system configured in stimulation mode.

FIG. 34 is a functional block diagram of an exemplary embodiment of aneurological microelectrode system configured in routing mode.

FIG. 35 is a functional block diagram of another embodiment of aneurological microelectrode system.

FIG. 36 is a schematic view of an embodiment of a neurological targetstimulator.

FIG. 37 is a schematic view of an embodiment of a neurological targetstimulator system.

FIG. 38A through FIG. 38D are a schematic views of various alternativeembodiments of a microelectrode array.

FIG. 39A through FIG. 39B are a schematic views of various alternativeembodiments of a microelectrode array.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Described herein are microelectrode array devices, and methods offabrication and use of the same, to provide highly localized andefficient electrical stimulation of a neurological target, such asindividual neurons, groups of neurons, and neural tissue as may belocated in an animal nervous system, such as deep within a human brain.In larger brain targets such as the Globus Pallidus, or in targets thatrequires high levels of neural stimulation, such as Brodmann Area 25,more electrodes are required within the target itself. A higher numberof electrodes, and more specifically a higher number of electrode edges,will increase the number of neurons that are captured by the electricfield for either stimulation or inhibition.

The stimulation can be highly localized, because the microelectrodeelements can be as small as only 2 μm or large as 2 mm in either ofdiameter or width. The relative spacing between such microelectrodeelements can also be as small as only 2 μm or as large as 2 mm. Although2 μm are indicated as lower limits to either dimension or spacing, otherembodiments are possible having dimensions and/or inter-element spacingof less than 2 μm, as may be practically limited by fabricationtechniques. Generally, microelectrodes of about 500 μm in diameter orwidth, with about a 500 μm spacing are particularly efficient instimulating neural tissue. An array of such microelectrode elements mayconsist of one or more such elements (e.g., sixteen elements), eachdisposed at a respective position, or site. This is in contrast tocurrently available stimulation leads, such as the Model 3387 or Model3389 DBS leads commercially available from Medtronic, Inc. ofMinneapolis, Minn. Such commercially available devices includerelatively large, cylindrical electrodes measuring about 1.5 mm inheight, and having a maximum of only four electrodes in use today fordeep brain stimulation.

Smaller microelectrode elements can be used to provide neurologicalstimulation that is highly localized and efficient because an array ofsuch microelectrodes can also be used to identify the stimulation regionof interest. For example, one or more microelectrode elements of such anarray of microelectrode elements can be used to detect and, in someinstances, record neuronal activity in the vicinity of thedetecting/recording microelectrode elements. Such refinement offered bythe relatively small size and/or spacing of the microelectrode elementscan be used to obtain a highly localized map of neuronal activity in theregion surrounding the implant. A suitably dimensioned microelectrodearray having multiple microelectrode elements positioned in a generalvicinity of a neurological target, can be used to locate a preciseneurological target without further repositioning, by identifying thoseone or more microelectrode elements located in a very specific region ofthe neurological target. The microelectrode array can be programmed tostimulate in a very specific region, for example, using only a certainnumber of the microelectrode elements to actively stimulate thesurrounding neurons and/or neuronal tissue, while other electrodeelements of the array remain inactive.

In some embodiments, an elongated device including such a microelectrodearray having elements with relatively small size and/or spacing can beused to obtain a highly localized map of neuronal activity in the regionsurrounding the implant. For example, such a device configured with alinear array of microelectrodes positioned along a length of a distalend of the device can be placed into a patient's brain. Preferably, theelements of the microelectrode array span a region including theneurological target. Neurological activity can then be independentlydetected by one or more of the microelectrode elements. The detectedactivity may be captured in a recorder or display device, allowing aclinician to identify which one or more of the microelectrode elementsis positioned closest to the intended target. Knowing a respectivelocation of each of the microelectrode elements along the device, anddetermining the distance to a reference, such as the patient's skull, aprecise location of the target can be determined as the distance along atrajectory of the device, measured from the reference to the particularmicroelectrode element. Beneficially, location of the target can bedetermined without any repositioning of the elongated device, therebysimplifying the medical procedure and reducing patient risk.

In some embodiments, the device is cutaneous, being removed after thetarget has been located, being replaced with a chronic probe, positionedat the determined target location. Alternatively or in addition, thedevice itself can be left in place as a chronic device, the samemicroelectrodes, or different ones, being used to record and/orstimulate the neurological target over an extended period.

One embodiment of a microelectrode device illustrated in FIG. 1 includesan elongated microelectrode probe assembly 100 sometimes referred to asan electrode lead. The microelectrode probe assembly 100 includes anelongated cylindrical member, or body 102 including a microelectrodearray 104 located relative to a distal end and one or more electricalcontacts located relative to a proximal end. The exemplarymicroelectrode probe assembly 100 includes a microelectrode array 104adjacent to its distal tip. The microelectrode array 104 has fourelectrically conductive, cylindrical microelectrode elements 103disposed along an exterior surface of a cylindrical substrate. Themicroelectrode elements 103 are microfabricated and wrapped around thecylindrical member 102. The microelectrode probe assembly 100 alsoincludes four electrically conductive, cylindrical contacts, or contactrings 106 a, 106 b, 106 c, 106 d (generally 106) distributed along alongitudinal axis of the proximal end of the assembly 100. In theexemplary embodiment, each of the microelectrode elements 103 is inelectrical communication with a respective one of the proximal contacts106 via a respective electrical conductor 108. In the exemplaryembodiment, all of the electrical conductors 108 are disposed within aninterior region of the elongated cylindrical member 102. There are noelectronics on this device 100. In use, signals are directed from animplantable pulse generator to the microarray. The length of thecylinder can vary.

The microelectrode probe assembly 100 is preferably sized and shaped forits intended neurological application. For example, the microelectrodeprobe assembly 100 may be at least partially placed within the centralnervous system. Alternatively or in addition, the microelectrode probeassembly 100 may be at least partially placed within other parts of thebody, such as the retina, the cochlea, the epidural space of the spine,and other locations within the peripheral nervous system. Thus thediameter and length of the microelectrode probe assembly 100 may varydepending on the particular anatomical target. Additionally, theconfiguration of the microelectrode array 104 is also sized and shapedfor an intended neurological target. The number, shape, orientation,size, and spacing of the microelectrode elements 103 of the array 104can be defined in response to the intended neurological target.

In at least some embodiments one or more of the microelectrode elements103 are sized and or spaced to record from and/or stimulate a singleneuron. The microelectrode probe assembly 100 can be used to detectand/or record neuronal activity at the neurological target. Neuronalactivity naturally occurring within the neurological target gives riseto local electromagnetic fields that can be detected by one or more ofthe microelectrode elements 103 of the microelectrode array 104. Forexample, electric fields produced by neurons will polarize one or moreof the microelectrode elements 103. Such polarization gives rise to anelectrical potential with respect to a reference, such as electricalground, or another one of the microelectrode elements 103. Such electricactivity can be further conducted to one or more of the cylindricalcontacts 106 through the internal electrical conductors 108. One or moreof the cylindrical contacts 106, in turn, can be connected to one ormore additional medical devices for further processing of the detectedelectrical activity. For example, the cylindrical contacts 106 can becoupled to a display device or recording device for displaying and/orrecording electrical activity from the neurological target.

Alternatively or in addition, one or more of the microelectrode elements103 can be used to electrically stimulate the neurological target. Forexample, one or more externally generated electrical signals can beapplied to one or more of the cylindrical contacts 106. These electricalsignals can be conducted through the internal electrical conductors 108to one or more of the microelectrode elements 103 of the microelectrodearray 104. Depending on the amplitude and polarity of the electricalsignals, an electrical field will be induced by the polarizedmicroelectrode elements 103. Electrical fields induced by suchpolarization can interact with one or more neurons at the neurologicaltarget.

Microfabricated Components

A microfabrication procedure can be used to implement electricallyconductive traces within an insulative substrate to form any of themicroelectrode array devices described herein, whether the array devicesare rigid or flexible. The microfabricated components include portionsof the microelectrode array assembly. The microelectrode array can beimplemented in a polymeric material such as polyimide or parylene andincludes thin film or plated layers of a metal or metal oxide with highcharge transfer capability such as platinum, platinum-iridium, iridium,iridium oxide or titanium. In some embodiments, other metals, metalalloys, and electrically conductive materials, such as dopedsemiconductors, conductive polymers, and conductive ceramics may beused. In some embodiments, the polymeric and metallic layers aredeposited sequentially and formed using established principles ofmicrofabrication such as spin coating, DC/RF sputtering,photolithography, plasma etching, and etching with a mask consisting ofa secondary or sacrificial material such as silicon dioxide orphotosensitive resist.

The metallic layer is formed to create one or more of the microelectrodearray elements and electrically conductive traces that connect the arrayelements to one or more of the electronics, when included, internalelectrical conductors of the elongated cylindrical member, and housing.In some embodiments, the microelectrode array includes multiple layers.For example, the polymeric layers serve to isolate the traces from eachother, while also providing the structure of the implant'sstimulating/recording tip. There are several fabrication methods whichcan be described to build such a microfabricated component.

The insulative substrate can be a polymer, such as a polyimide orparylene but can also be polyurethane or polysiloxane (silicone), or anyother suitable insulator. For substantially non-flexible, or rigidembodiments, a rigid or semi-rigid substrate can be included. In someembodiments, the microelectrode array device is formed on at least onesurface of a rigid substrate, such as a planar ceramic member.Alternatively or in addition, one or more rigid or semi-rigid supportingmembers can be attached during fabrication to provide a desired amountof rigidity. Generally, the microfabricated component can be fabricated,for example, using a series of additive and subtractive processes thatproduce a stack of materials.

Mechanical components of the implantable neurological probe assembly 100include the elongated cylindrical member 102, which can be a simplepolymeric cylinder. In some embodiments the cylindrical member may becomposed of two concentric tubes with wire traces wrapped around theinner tube, in the space between the concentric tubes. The elongatedcylindrical member 102 can vary in length and diameter but is generallyat least about 28 cm long, and around 1.27 mm in diameter. In someembodiments, the microfabricated component is wrapped around an externalsurface of the cylindrical member 102. In some embodiments, themicrofabricated component is wrapped around an additional tube at thedistal end of the cylindrical member 102. Alternatively or in addition,the microfabricated components can be attached to the cylindrical member102 to protrude at the distal tip, from the cylindrical member'sinterior. The cylindrical member 102 also contains electrical wires 108within that connect at one end to the microfabricated component, atanother end to the cylindrical contacts 106 for interconnection to animplantable pulse generator. In some embodiments, one or more of themicrofabricated components and the elongated cylindrical member 102include one or more electrical components.

The electrical components can be discrete or microelectronic parts.Their purpose is to filter, route, generate, or process signals to andfrom the microelectrodes. They can be attached to the microfabricatedpart during production, or bonded afterwards. They will generally becontained within the mechanical component.

The neurological probe 100 can be implanted near a neurological target,such as a target brain structure, using common neurosurgical techniquessuch as stereotaxy or endoscopy. The neurological probe 100 can beinserted without support, or within a supporting cannula having an innerdimension slightly larger than the outer dimension of the device. Thecannula, when used, would be retracted once the neurological probe 100has been suitably positioned. In some embodiments a lumen along the axisof the cylindrical member 102 permits the insertion of a rigid styletwhich renders the neurological probe 100 rigid during surgicalimplantation. This is particularly helpful during insertion, positioningand repositioning of flexible embodiments of the neurological probe 100.The stylet is removed after implantation leaving the probe in itssurgical target.

A clinician can connect one or more of the microelectrode elements to adisplay unit or a recording unit through the cylindrical contacts 126.The recording unit, not shown, allows a clinician to identify certainregions of the brain according to their electrical activity. In someembodiments, such recording information can be processed automatically,through the use of a suitably programmed computer processor. Theelectrodes used to record from the brain can be the same electrodes asthose used to stimulate tissue. The recording electrodes can also beseparate from those used to stimulate the brain. This situation might bepreferred because electrodes destined for recording may be different insize and design than those for stimulation.

The operator can connect the electrodes to an external stimulationsource or an implantable source. In either instance, the source caninclude a pulse generator for applying signals to the electrode sites.The signals from such a pulse generator can be connected directly to theelectrodes, or they can be preprocessed using electronics embedded inthe device. The electronics can filter certain parts of the originalsignal. If there are more electrodes than signals, the electronics canroute or otherwise interconnect the stimulation source as necessary.

A perspective view of the portion of a human anatomy is illustrated inFIG. 2, showing implantation of an exemplary elongated microelectrodeprobe assembly 124 position for interaction with a neurological targetlocated deep within the brain. A distal portion of the microelectrodeprobe assembly 124 is positioned at the neurological target 130, in thisinstance located within the human brain 132. In some embodiments theproximal end of the microelectrode probe assembly 124 is connected to afirst medical device 128. For example, the first medical device 128 mayinclude an electronic assembly implanted external to the brain 132 tominimize invasion into the brain and flesh or to facilitate wirelessaccess to the electronic assembly 128. Alternatively or in addition, asecond medical device, which again may include an electronic assemblysuch as a pulse generator 122 can be implanted at a remote portion ofthe subject body. As shown, a second electronic assembly 122 isimplanted within a chest cavity 120. When one or more medical devices,such as the exemplary pulse generator 122 are located remotely in thismanner, a cable 126 may also be implanted within the subject's body tointerconnect the pulse generator 122 to the electronic assembly 128,when present or directly to cylindrical contacts located at the proximalend of the microelectrode probe assembly 124.

Referring now to FIG. 3, a cross-sectional view of a portion of ananatomy 148 is shown, illustrating an exemplary microelectrode probeassembly 140 positioned at a neurological target 150 (e.g., subthalamicnucleus, shown). The microelectrode probe assembly 140 includes an arrayof microelectrode elements 142 a, 142 b, 142 c, 142 d (generally 142)distributed along an elongated, cylindrical supporting structure 144.Preferably, the microelectrode probe assembly 140 is shaped and sized toallow one or more of the microelectrode elements 142 to be positioned atthe neurological target 150. To this end, materials used in constructionof microelectrode probe assembly, as well as one or more of itsconstruction features, size, shape, and orientation can be selected forbiocompatibility.

As illustrated, one or more of the microelectrode elements 142 c of themicroelectrode probe assembly 140 are positioned in intimate contactwith the neurological target 150. In more detail, each microelectrodeelement is configured here as an annular array of sub-elements 145, 151.The sub-elements 145, 151 can be distributed about a circumference ofthe probe assembly 140, at a common axial displacement from the distalend. It is understood that some sub-elements of such an annular array142 c can be in contact with the neurological target, while othersub-elements of the same annular array 142 c are not (as shown). One ormore additional microelectrode elements 142 of the probe assembly 140may reside at locations not in the immediate vicinity of theneurological target 150. In at least some embodiments, one or more ofthe microelectrode elements 142 are remotely accessible from a proximalend of the probe assembly 140 via one or more electrically conductiveleads (not shown).

In at least some embodiments, selectable sub-elements 145, 151 can beactivated to record and or stimulate the target 150. For example,recordings of neurological activity from sub-elements 145 in contactwith the target 150 can be used to identify the location of the target150 relative to the probe assembly 140. As determined from therecordings, only those sub-elements 151 in contact with the target maybe activated to stimulate the target. Depending upon the location of thetarget, this may result in an annular array 142 stimulating a selectableangular region about the probe assembly 140.

Any of the supporting structures described herein, such as thesupporting structure 144 illustrated here can be a ridged, or semiridged structure, such as a polymeric cylinder. Alternatively or inaddition, the structure can be a flexible structure, such as one or moreflexible substantially non conducting substrate (i.e., a bi-electricribbon) onto which the microelectrode elements 142 are formed aselectrically conductive film layers. The one or more microelectrodeelements 142 are in communication with electronic circuitry (not shown)through one or more electrical leads (not shown) that can be routedthrough an internal lumen of a supporting structure 144 and/or formedusing elongated film layers along a flexible, ribbon like supportingstructure 144.

In some embodiments, the microelectrode elements 142 can be placed intothe brain generally for recording and/or stimulation of the cortex andfor deep brain stimulation and/or recording of neurological targetsincluding the subthalamic nucleus and the globus pallidus. Themicroelectrode elements 142 can also be placed in other parts of thebody, such as the retina, the spine, the peripheral nervous system forneural recording and/or neural stimulation of such portions of an animalanatomy. Although microelectrodes are discussed generally throughout thevarious embodiments, there is no intention to limit the upper or lowersize of the microelectrodes. The devices and methods described hereinare generally scalable, with a microelectrode size determined accordingto the intended application. For at least some of the neurologicalapplications, microelectrodes are dimensioned sub-millimeter. In someembodiments, microelectrodes are dimensioned sub-micron. In someembodiments, the microelectrodes are formed as planar structures havinga diameter of about 50 μm that are arranged in a linear array withcenter to center spacing of about 100 μm. The planar structure of themicroelectrodes can have regular shapes, such as circles, ellipses,polygons, irregular shapes, or a combination of such regular and/orirregular shapes.

This probe assembly 140 is implantable near a neurological target, suchas a target brain structure, using common neurosurgical techniques suchas stereotaxy or endoscopy. The device might be inserted without supportor within a cannula which may have an inner dimension slightly largerthan the outer dimension of the device. Alternatively, or in additionto, the device may have a rigid stylet miming along its central axiswith an outer diameter that is smaller than the inner diameter of anaxial lumen in the device. When used, such a cannula, or a stylet, isgenerally retracted once the device is in position.

The operator can connect the probe assembly 140 to a recorder unitconfigured to identify certain regions of the neurological target (e.g.,the brain) according to the electrical activity detected by the probeassembly 140. In some embodiments, the microelectrode elements 142 usedto record from the neurological target 150 can be the samemicroelectrodes as those used to stimulate the target in applications inwhich both recording and stimulation are accomplished. Alternatively orin addition, the microelectrode elements 142 used to record from theneurological target 150 can be separate microelectrode elements 142 fromthose used to stimulate the target 150. This is demonstrated in thisembodiment, in which each microelectrode assembly includes one or morerecording electrodes 145 and one or more stimulating electrodes 151. Asshown, the dedicated recording electrode 145 is smaller than dedicatedstimulation electrode 151. In some embodiments, microelectrodes destinedfor recording (e.g., 145) may differ in one or more of size, shape,number, and arrangement from those microelectrodes destined forstimulation, e.g., using different microelectrodes.

The microelectrode elements 142 configured for stimulation can beconnected to a stimulation source through one or more interconnectingleads. In some embodiment, at least a portion of the stimulation sourcecan be extracorporeal. Alternatively or in addition, the stimulationsource can be in vivo. Any implanted elements of the stimulation sourceare preferably fabricated and/or contained with a hermetically sealed,bio-compatible envelope. Such bio-compatible packaging of signal sourcesis well known, for example, in the area of artificial pacemakers. Thestimulation source, when provided, may be a controllable signalgenerator producing a desired signal according to a prescribed input.For example, the signal generator may receive an input indicative of adesired output stimulation signal frequency. Such output stimulationsignals can have a variety of wave forms, such as pulses, chargedbalanced pulses, sinusoidal, square wave, triangle wave, andcombinations of such basic wave forms.

In some embodiments, the stimulation source includes a pulse generatorfor applying signals to the microelectrodes site. The signals from thepulse generator can be connected directly to the microelectrodes, orthey can be preprocessed using electronics. In some embodiments, suchpreprocessing electronics are embedded within the implantable device.The preprocessing electronics can filter certain parts of an originalsignal, such as a cardiac pacemaker signal, in order to select preferredfrequency components of the original signal that are at or near a peakresistance frequency of the microelectrodes. For embodiments in whichthere are more microelectrodes than signals, electronics can route thestimulation signals to preferred one or more of the microelectrodes.

Referring now to FIG. 4 a more detailed view of a distal end of themicroelectrode probe assembly 100 as shown. The microelectrode array 104includes a formable planar substrate 160. One or more electronicallyconducting regions 162 are disposed along portions of the formableplanar substrate 160. The microelectrode probe assembly 100 can beformed using a polyimide structure (e.g., 160) containing multiplemicroelectrode elements wrapped and molded in place around an elongated,cylindrical polyurethane body. In the illustrative embodiment, theelectronically conducting regions 162, or microelectrode elements, arethin-film conducting bands extending around a substantial circumferenceof an external surface of the elongated cylindrical member 102. Asshown, there are four such electrically conducting bands 162 spacedapart, each located at a different respective distance measured from adistal tip of the elongated microelectrode assembly 102. The fourconducting bands 162 can be electrically coupled to an implantable pulsegenerator. In some embodiments, one or more of the conducting bands arecoupled to the implantable pulse generator through an impedance matchcircuit (not shown). The electrically conductive electrode width in thisexample is about 700 μm (the particular width is selectable and, forexample, can range from 2 μm or less to 2 mm or more), there are foursuch microelectrode rings which encircle the body. The electricallyconductive microelectrode elements 162 can be formed using metals,suitably doped semiconductors, conductive polymers, conductive ceramics,and combinations thereof.

In at least some embodiments the formable planar substrate 160 includesa longitudinal extension 164. This longitudinal extension 164 mayinclude one or more electrical circuit elements such as one or moreelectrically conductive wire-lead contacts 168 as shown. One or more ofthe electrically conductive circuit elements, such as the wire-leadcontacts 168 may be in electrical communication with one or more of theelectrically conducting bands 162 through interconnecting traces 166extending between the wire-lead contacts 168 and the electricallyconducting bands 162. As illustrated, at least a portion of themicroelectrode array 104 is located along an external surface of theelongated microelectrode probe assembly 100. Other portions such as thelongitudinal extension 164 maybe located within an interior portion ofthe elongated cylindrical member 102. Four internal electricalconductors, or leads 108, are illustrated extending along an interiorportion of the elongated cylindrical member 102. Distal tips of each ofthe internal electrical conductors 108 are in electrical communicationwith a respective one of the wire-lead contact 168 as illustrated.

An exemplary embodiment of a microelectrode array 180 is illustrated inFIG. 5. The microelectrode array 180 can be prepared as amicro-electromechanical system (MEMS). Such a MEMS film device 180 canbe prepared from a substantially electrically insulative planarsubstrate 182 onto which the electrically conductive elements areformed. For example, a dielectric planar substrate 182 is prepared toinclude electrically conductive surfaces corresponding to the multipleelements of the microelectrode array. As shown, a four elementmicroelectrode array of electrically conducting elements 184 a, 184 b,184 c, 184 d (generally 184) is formed on a polyimide substrate. In someembodiments, the formable planar substrate 182 includes a longitudinalextension 186. One or more of the microelectrode array elements 184 canbe connected to one or more other circuit elements such as lead wiretraces 186 provided on the longitudinal extension 185. Such a device canbe prepared using standard MEMS techniques by which the substrate andconductive elements are prepared in a planar configuration and laterformed into a non-planar shape. For example, the four-elementmicroelectrode array 184 can be formed into a substantially cylindricalshape to accommodate an outer surface of an elongated cylindrical memberof a microelectrode probe assembly.

Referring next to FIG. 6, the MEMS device 180 is shown attached at adistal tip of an elongated cylindrical member 192. The electricallyconductive surface of the four-element microelectrode array 184 remainsexposed about the outer surface of the elongated cylindrical member 192.Thus, the microelectrode array 184 is positioned for intimate contactand interaction with any neurological target into which the elongatedcylindrical member may be placed.

An alternative embodiment of a neurological probe 200 is shown in FIG.7A. This neurological probe 200 also includes a formable film substrate205 shown placed at a distal end of an elongated cylindrical body 202.In the illustrated embodiment, the cylindrical body 202 is formed by twocoaxial cylindrical members. At a proximal end are eight cylindricalcontacts 206, which electrically connect the proximal end to the filmsubstrate 205 at the distal end through lead wires within the coaxialcylindrical members 202.

Referring next to FIG. 7B, a more detailed view of the distal end isshown. Formed along an outer surface of the formed cylindrical substrate205 are multiple circumferential segmented microelectrode elements 204and 207 spaced apart along both longitudinal and circumferential axes.In this exemplary embodiment eight such conductive microelectrodeelements are included. Microelectrode elements 204 are segmented suchthat three microelectrodes at a common axial location are disposed abouta circumference of the neurological probe 200, referred to herein assegmented elements. Such segmented elements that are independentlyaddressable allow for stimulation a selectable angular region about theprobe assembly 140. For example, only those sub-elements on one side ofthe probe 200 can be activated to selectively treat a target along thesame side of the probe. More than one sub-element can be activated toselectively treat a desired angular region disposed about the probe,including a region tending 360 deg. or less. In this regard, the probecan be said to focus energy toward a desired region.

Microelectrode elements 207 are not segmented, therefore one electrodecovers the entire circumference of the neurological probe 200. Theassembly can include an end cap 209, which covers the end of thecylindrical tubing. The assembly can also include a support tube 215onto which the microelectrode film can be attached, e.g., by gluing orheating. In this embodiment, each contact of the eight cylindricalcontacts 206 is electrically coupled to a respective one of themicroelectrodes 204, 207.

FIG. 7C demonstrates the shaping required for the microelectrode film205 in order to be assembled. The microelectrode film 205 also includesa longitudinal extension 206. The extension 206 incorporates contactpads 211, each pad 211 in electrical communication with a respective oneof the microelectrode element 204, 207, for example, through electricaltraces. Both the distal and proximal ends of the microelectrode film 205are reshaped, for example using heating, into a cylindrical shape asshown. Other shapes are possible, depending on the cross-sectionalprofile of the support tube 218 (e.g., triangular, oval, rectangular).

FIG. 7D illustrates the assembly of the neurological probe 200 in moredetail. The assembly constitutes two overlapping, concentric cylindricalmembers 213 and 214. Inner cylindrical member 213 defines a lumen with atypical diameter of 400 μm. The outer diameter can be 1 mm, but must beless than the inner diameter of outer cylindrical member 214. Bothcylindrical members 213 and 214 can be composed of a polymeric, rigid ornon-rigid (e.g., semi-rigid or flexible) material such as polyurethaneor silicone. The assembly also constitutes eight lead wires 212extending longitudinally in a space defined between the cylinders 213,216. In some embodiments, the lead wires 212 are helically wrappedaround inner cylindrical member 213. Lead wires 212 generally have adiameter of 50-125 μm. The assembly may optionally include a rigid orsemi-rigid support tube 215 at its distal end. The tube 215 is used as asupport structure onto which the microelectrode film 205 can beattached. The microelectrode film 205 is attached via its contact pads211 to electrical lead wires 212, each lead wire 212 contacting arespective one of the contact pads 211. The tube 215 can cover theseconnections adding strength to their structure. The microelectrode film205 is then wrapped in the direction of the arrow. Finally, end cap 209covers and seals the cylindrical members 213 and 214. The end cap can beshaped, for example, having a blunt profile, as shown.

FIG. 7E demonstrates an image of an assembled neurological probe 200.The different components described in FIG. 7A through FIG. 7D arevisible including the microelectrode array film 205, the inner tubing213 and the outer tubing 214. In this embodiment the distal support tube215 has been implemented as a laser cut stainless steel tube.

Another embodiment of an elongated microelectrode probe assembly 220 isillustrated in FIG. 8A and FIG. 8B, including a microelectrode arrayassembly 224. The microelectrode array assembly 224 is positioned at adistal end of an elongated cylindrical member 222. Once again, one ormore electrically conductive, cylindrical contacts are positioned at aproximal end of the elongated cylindrical member. As shown, there arefour such cylindrical contacts 226. In other embodiments, there may bemore or fewer contacts. The microelectrode array assembly 224 alsoincludes a microelectronics assembly 233 positioned along an offsetlongitudinal extension 232 of the assembly. The longitudinal extension232 is offset such that the microelectronics assembly 233 is containedwithin an interior region of the elongated cylindrical member 222,thereby protecting the microelectronics assembly 233 from interactionwith the surrounding biological environment. One or more internalelectrical conductors 228 extend from the longitudinal extension 232 toone or more of the cylindrical contacts 226.

In more detail, referring to FIG. 8B, the longitudinal extension 232 isalso in electrical communication with the conductive electrodes of themicroelectrode array 230 through one or more lead traces 234. Also shownare the connections between the internal electrical conductors 228 and aproximal end of the longitudinal extension 232. Thus, in a recordingmode, electrical activity from a neurological target can be detected byone or more of the microelectrode contacts 231 of the microelectrodearray 230. The electrical signals are then routed through the leadtraces 234 to the microelectronics assembly 233. The microelectronicsassembly 233 may process the detected electrical signals, for example,through pre-amplification and routing. Ultimately the processedelectrical signals detected from the neurological target are routedthrough the internal electrical conductors 228 to the cylindricalcontacts 226. One or more external medical devices such as a recordermay be connected to the elongated microelectrode assembly 220 throughthe cylindrical contacts 226 for display and or recording of thedetected electrical activity.

One or more of the cylindrical contacts 226 can be used to communicatewith the microelectronics assembly 233 through one or more of theinternal electric conductors 228 in order to remotely or externallycontrol operation of the microelectronics assembly 233. For example, anexternal signal may be used to select which one or more of themicroelectrode contacts of the microelectrode array 230 are selected forrecording. In some embodiments recording can be accomplished for all ofthe microelectrode contacts of the microelectrode array 230.

Alternatively or in addition, the microelectronics assembly 233 mayinclude a multiplexer for combining the signals from more than one ofthe microelectrode elements 231 onto one of the cylindrical contacts226. Alternatively or in addition, such multiplexing techniques can beused to combine one or more of the cylindrical contacts 226 to one ofthe microelectrode elements 231. For example, two contacts 231 can becoupled to one of the distal contacts 226, such that four contacts 226are sufficient for accessing all eight microelectrode elementssimultaneously. Such multiplexing may include any suitable form, such astime division multiplexing, frequency division multiplexing, codedivision multiplexing, and combinations of one or more of thesetechniques.

In some embodiments the microelectronics assembly 233 perform at leastsome level of processing of the detected neurological activity. In someembodiments the microelectronics assembly 233 may be a purely routingdevice connecting one or more selected microelectrode elements 231 toone or more of the cylindrical contacts 226. Such a microelectronicsassembly 233 may be a simple switch or router device. Such routing mayinclude electromechanical switches, reed switches, and electronicswitches, such as transistor (e.g., field effect transistor) switches.The switches can be configured in a matrix fashion to allow one or moreof the microelectrode elements 231 to be in communication with one ormore of the microelectronics assembly 233 and the internal electricalconductors 228 based on a control input signal as may be received froman external source through one or more of the contacts.

In some embodiments, the microelectronic device may include signalconditioning circuitry such as one or more of amplification, filtering,and attenuation. For example, in detection or recording mode, one ormore low noise preamplifiers may be included for boosting detectedsignal level to improve their detectability and recording quality at thecylindrical contacts 226. Such signal conditioning may include one ormore of electronic filtering to tailor a frequency spectrum of thedetected signal and attenuation. Such electronic filtering can beaccomplished with any suitable filter known to those familiar withelectronic signal processing. Such filters may include low pass, highpass, band pass and combinations of one or more of these. The filtersmay be implemented with standard circuit elements, such as inductors,capacitors, and resistors. Alternatively or in addition, at least someof the filters may be implemented using digital signal processingtechniques.

Additional processing can be performed to assess the recorded signalsand to determine the location of a preferred neurological target.Through careful configuration of the microelectronic contacts in theirsize, location and configuration, it is possible to locate a targetneurological site. For embodiments in which the microelectrode contactsare dimensioned on the order of target neurons it may be possible torecord activity of individual neurons independently. Themicroelectronics assembly 233 may include one or more of anApplication-Specific Integrated Circuit (ASIC), commonly availableelectronics modules, such as microprocessors, electronic memoryelements, communications devices, combinational logic, powerconditioning, and the like.

An exemplary longitudinal extension of a MEMS film device is illustratedin FIG. 9. The longitudinal extension 232 includes a planar filmsubstrate 242. The substrate 242 includes a first group of one or moreelectrical contacts in the form of bonding pads 244, sized andpositioned to accommodate one or more devices of the electronicsassembly 230 (FIGS. 8A, 8B). The substrate 242 also includes a secondgroup of one or more additional electrical contacts in the form of wirebonding pads 246, sized and positioned to accommodate interconnection toone or more of the interconnecting lead wires 228. At least some of thebonding pads 244 of the first group are coupled to respective lead wiretraces 248 interconnecting the bond pads 244 to respective ones of themicroelectrode contacts 231. As illustrated in FIG. 10, the longitudinalextension 232 includes the microelectronics assembly 233 housed thereonand the interconnecting lead wires 228 coupled to the second group ofbonding pads 246.

Another embodiment of an elongated microelectrode probe assembly 420 isillustrated in FIG. 11A and FIG. 11B. The assembly 420 includes amicroelectrode array assembly 260 at a distal tip of the probe assembly420 as shown. This microelectrode array assembly 260 can be anymicroelectrode array including any of the microelectrode arraysdescribed herein. The assembly 420 also includes one or more cylindricalcontacts 426 a, 426 b, 426 c, 426 d (generally 426) at a proximal end,as shown. The microelectrode array assembly 260 and cylindrical contacts426 are disposed along a flexible elongated cylindrical member 422. Thecylindrical member 422 includes an elongated open-ended lumen 424,accessible from an open end 430 located at a proximal end of the probeassembly 420.

One or more internal electrical conductors 428 extend from themicroelectrode array assembly 260 to the one or more cylindricalcontacts 426. The internal electrical conductors are configured so asnot to interfere with interior volume of the open ended lumen 424 orwith flexibility of the elongated cylindrical member 422. In theillustrated embodiment, four such electrical conductors 428 are shownextending helically along the length of the elongated cylindricalmember, between the microelectrode array assembly 260 and thecylindrical contacts 426. These helically wound internal electricalconductors 428 reside within the material of the flexible elongatedcylinder 422 between an exterior surface and an interior wall of theopen ended lumen 424.

Beneficially, an elongated rigid guide member, such as a stylet, ortrocar (not shown) can be inserted into an open end 430 of the openended lumen 424 extending along a substantial length of the elongatedflexible cylindrical member 422 to provide temporary rigidity as may benecessary during insertion and/or removal procedures of the elongatedelectrical probe assembly 420. When employed during an insertionprocedure, such a stylet provides rigidity as the elongated electricalprobe assembly 420 is inserted into a neurological target site. Onceinserted at the target site, the stylet can be removed from the proximalopen end 430. The remaining elongated electrical probe assembly 420remains positioned at the target site, while also providing substantialflexibility along its extended length. Such flexibility offersadvantages for patient comfort and response to any movement of the localanatomy to promote prolonged placement of the microelectrode arrayassembly 260 at the neurological target site. The stylet may beconfigured as a straight element. In some embodiments, at least aportion of the stylet may include a non-linear region, such as a curve,as may be beneficial to facilitate insertion and/or removal of theelongated electrical probe assembly 420.

As shown, the microelectrode array assembly 260 extends for a length ‘T’along longitudinal axis. The elongated flexible cylindrical member 422has a diameter ‘D’. Four cylindrical contacts 426 at the proximal endcan provide access to power 426 a, electrical ground 426 b, control 426c, and signal or data 426 d.

A more detailed view of a distal portion of the elongated electricalprobe assembly 420 shown in FIG. 11B illustrates distal ends of each ofthe helically wound internal electrical conductors 428, connected torespective lead wire bonding pads 436 as may be provided on alongitudinal extension 434 of the microelectrode array assembly 260.Also visible is the distal portion of the open ended lumen 424, having adistal end 432 located relatively close to a proximal end of thelongitudinal extension 434. Thus, the open ended lumen 434 extends alongnearly the entire length of the elongated flexible cylindrical member422. When the stylet is inserted within the open ended lumen 424 andextends toward the distal end 432, the elongated flexible cylindricalmember 422 has temporary rigidity along substantially its entire length.

A more detailed illustration of an embodiment of the distal end of theelongated probe assembly 420 is shown in FIG. 11C. The device includes amicroelectrode array 260, located adjacent to the distal tip 438. Themicroelectrode array assembly 260 includes a longitudinal extension 434housing one or more microelectronic devices 440 and including electricalcontacts, each in respective communication with one of the internallyelectrical conductors 428.

A more detailed illustration of the assembled microelectrode film 260 isillustrated in FIG. 11D. The assembly 260 includes a hollow cylindricalsubstrate 262. The exemplary embodiment includes sixteen semi-annularmicroelectrodes 268 arranged in annular sub-arrays positioned atrespective distances along a longitudinal axis of the cylindricalsubstrate 262 for example being measured from a distal end. In theexemplary embodiment, each annular sub-array includes four stimulationelectrodes 268 and four recording electrodes 269. Other numbers ofsub-array elements are possible, and it is not necessary that the numberof stimulation electrodes 268 be equivalent to the number of recordingelectrodes 269 for any given sub-array. In some embodiments, eachsub-array is identical, while in other embodiments, they differ.

In some embodiments, each stimulation electrode element 268 extendsalong an arc length greater than 10° but less than 180°. Each recordingelectrode 269 extends along an arc length substantially less than 90°such that the combination of stimulation electrode elements 268 andrecording electrode elements 269 are disposed about 360° of thecylindrical substrate 262 with suitable spacing provided between each ofthe adjacent elements 268, 269. As illustrated, the stimulationelectrode elements 268 appear as stripes located about their respectivedistances along the central axis; whereas, the recording electrodesappear as small circles, or dots.

The particular shape of the recording electrode elements 269 can becircular, elliptical, polygonal, such as squares, triangles, diamonds,hexagons, and the like. The shape of the stripe ends of the stimulationelectrode elements 268 adjacent to the recording electrode 269 may beangular (e.g., square) or curved. As shown in the figure, a referenceangle is measured with respect to a seam at 0° extending around thecircumference. The recording electrodes 269 are located adjacent to theseam 264 at approximately 0°. A second recording electrode locatedopposite to the first resides at approximately 90°. Likewise, thestimulation electrode element 268 is centered at approximately 45°,between approximately 15° and 75°. A second stimulation electrode 268 islocated centered at 135° and also extending between approximately 105°and 165°. A third recording electrode 269 is located at approximately180°. A third stimulation electrode 268 is located centered at 225°,extending between approximately 195° and 255°. A fourth recordingelectrode 269 is located at approximately 270°. A fourth stimulationelectrode 268 is located centered at 315° extending betweenapproximately 285° and 345°.

Also shown is a longitudinal extension to the substrate 272 including inthis example thirty two electronic device contacts 274, each one inelectrical communication with a respective one of the dedicatedrecording or dedicated stimulating electrodes via interconnecting leadtraces. Also disposed on the longitudinal extension 272 are one or morewire lead contacts 276. In the illustrative example, four such wire leadcontacts 276 are provided.

Illustrated in FIG. 12 is an electronic circuit schematic diagram forhalf of the microelectrode array assembly 260 shown in FIG. 11D. Shownalong the right hand portion of the schematic diagram are the eight ofthe sixteen stimulation electrode elements 268 a through 268 h(generally 268). Each one of these elements 268 is in electricalcommunication with a respective electronic device contact 274 a through274 d and 274 m through 274 p (generally 274). Also illustrated alongthe right hand portion of the schematic diagram are eight of the sixteenrecording electrode elements 269 a through 269 h (generally 269).Similarly, each of the recording electrode elements 270 is in electricalcommunication with a respective electronic device contact 274 e through274 h and 274 j through 274 l. For illustrative purposes, the schematicdiagram includes a representative electronic device 280. For brevity,the schematic diagram includes only eight recording and eightstimulation contacts but a full schematic diagram for all thirty-twocontacts is similar. In this electronic device may include one or moreof a switch or router, a preamplifier, a signal conditioner, amultiplexer, and a controller. The electronic device 280 is inelectrical communication with all sixteen of the electronic devicecontact elements 274 a through 274 p.

The electronic device 280 is in further communication with each of thefour wire lead contacts 276 a through 276 d (generally 276). In theillustrative example, the first wire lead contact 276 a is used forsupplying electrical power to the microelectronic device and/or one ormore of the stimulation electrode elements 268. The second wire leadcontact 276 b is used to provide an electrical ground contact. Thisground contact 276 b may include earth ground, another electrical groundwithin the system, such as a chassis ground of a medical deviceconnected to the electronic device 280, or simply a signal return line.A third wire lead contact 276 c corresponds to a control signal that maybe used to provide control inputs from an operator or other medicaldevice, to control configuration and/or operation of the electronicdevice 280. Alternatively or in addition, the control signal contact 276c may be used for control signals from the electronic device 280 toanother medical device. A fourth wire lead contact 276 d corresponds toa signal contact as may be used for directing electrical activitydetected by one or more of the recording electrode elements 269 to arecording or display device. Alternatively or in addition, the signalcontact 276 d may be used for directing electrical stimulation signalsfrom another medical device to one or more of the stimulation electrodeelements 268.

Referring again to FIG. 11D, the stimulation electrodes 268 areconfigured to have a relatively low electrical impedance; whereas, therecording electrodes 269 are configured to have a relatively highelectrical impedance. A relatively low impedance stimulation electrodes268 are therefore well suited for transfer of electrical charge transferto surrounding tissue at a neurological target site. Also, the relativehigh impedance recording electrodes 269 allow for detection ofelectrical activity from a neurological target site.

FIG. 13A displays an additional embodiment of a neurological probe 200,incorporating embedded microelectronics. The neurological probe 200incorporates a microelectrode film 202, and cylindrical member 203composed of two concentric cylindrical tubes, and eight electricalcontacts 201 that permit electrical connection from the distal end tothe proximal end through eight lead wires wrapped around the innercylindrical member.

FIG. 13B provides a more detailed view of an embodiment of the distalend of the neurological probe 200. The metallic stimulation electrode248 has dimensions in this example of about 1000 μm in length, and 600μm in width. In some embodiments, the length measured along thelongitudinal axis can range from 2 μm to 2 mm In some embodiments, thewidth may cover the entire circumference, and can range from 2 μm to 4mm. The metallic recording electrode 249 has dimensions in this exampleof 150 μm in diameter. It is generally smaller than the stimulationelectrode 248.

The distal end incorporates a support tube 229, that serves as a supportstructure for the microelectrode film 202 and as a protective enclosurefor the microelectronic circuit and connections within. In this examplethe tube 229 has a length of 8 mm, an inner diameter of 1.05 mm, and anouter diameter of 1.25 mm. It may be implemented in a rigid, orsemi-rigid material such as stainless steel, or a biocompatible polymersuch as PEEK (polyetheretherketone).

The embodiment also demonstrates the outer cylindrical member 203 whichis implemented with an outer diameter of 1.27 mm, and an inner diameterof 1.05 mm. It is generally implemented in polyurethane or silicone.Along its lumen are wrapped the lead wires 221 that electrically connectthe proximal and distal ends of the neurological probes. The outercylindrical member 203 can be connected to the support tube 229 by formfitting or gluing.

The embodiment also demonstrates an end-cap 241 which can be implementedas a plug to seal the ends of the two concentric tube structures. Themicroelectrode film 202 is connected to the inner volume by an extension208 that leads to the embedded microelectronic element and lead wires221.

Referring now to FIG. 13C, a cutaway view of the distal end of theneurological probe 200 is provided in order to identify themicroelectronic element at its interior. The longitudinal extension isoffset from an external surface of the cylindrically formed substrate202 such that the longitudinal extension 206 and any microelectronicdevices 210 mounted thereon would be containable within an interiorregion of the elongated cylindrical member housing the formable filmsubstrate 202. In the illustrative embodiment, the formable filmsubstrate 202 including the conductive electrodes is wrapped around acylindrical body 229 located at the distal end of the neurologicalprobe. For applications including multiple electrode rings, a selectioncircuit, such as a switch or router, can be included to selectably routestimulation or recording signals to/from one or more of themicroelectrode rings thereby stimulating or recording from a selectablelocation within the neurological target depending upon whichmicroelectrode ring(s) is in use. Such stimulation signals may be routedfrom the implantable pulse generator 122 (FIG. 2) and applied to achosen microelectrode ring.

As shown in FIG. 13D, the microelectrode film can be initially formed asa flat element onto which a microelectronic circuit element is mountedbefore, or after, it is assembled into two concentric cylinders. Thelongitudinal extension 206 can be configured to accommodate one or moremicroelectronic devices 210. One or more of any such microelectronicdevices 210 included thereon can be in electrical communication with oneor more of the microelectrode elements 248 and 249 through one or moreinterconnecting conductive electrical traces 208.

Various configurations of the microelectrode elements are illustrated inFIG. 14 through FIG. 15. Referring first to FIG. 14A, a microelectrodearray 300 is illustrated placing many relatively small microelectrodes302 around a central cylinder. In the exemplary embodiment, eight suchelements 302 are located at respective positions around 360°circumference of the cylinder, forming an annular microelectrode pattern303. In some embodiments, the angular displacement between adjacentelements may be uniform as shown (e.g., eight elements spaced apart fromeach other by 45°). Alternatively or in addition, the angulardisplacement between at least some of the adjacent elements 302 of theannular microelectrode pattern 303 may be non-uniform. Additionalannular patterns of elements can be positioned along the cylinder. Forexample, the same pattern can be repeated at different distances alongthe cylinder as measured with respect to an end of the array 300. Thedistance between adjacent annular patterns 303 may be uniform.Alternatively or in addition, the distance between adjacent annularpatterns 303 of the microelectrode array 300 may be non-uniform. In theexemplary embodiment, there the array 300 includes four identicalannular patterns 303 uniformly spaced apart along the central cylinder.

In the exemplary embodiment, the annular microelectrode pattern 303includes eight microelectrode 302 discs, each having a diameter of about300 μm, uniformly distributed and wrapped around a 1.27 mm diametercylinder. The microelectrodes 302 could be other shapes, such asellipses, polygons, such as squares, triangles, diamonds, hexagons, andthe like. One or more of the shapes and sizes of the microelectrodes 302may vary within the annular microelectrode pattern 303. For example,sizes may range from 2 μm or less, to 1 mm or larger. The electronicsrequired to apply electrical signals to the microelectrode sites, or torecord neural activity from the sites, are embedded within the centralcylinder.

An alternative embodiment of the invention illustrated in FIG. 14B showsseveral microelectrode elements 312 configured lengthwise, extendingalong a longitudinal axis of the cylinder and disposed at respectiveangles measured about a circumference of the cylinder. In the exemplaryembodiment, each microelectrode element 312 is a strip having a diameterof about 300 μm and length of approximately 1.88 mm, extending along thelength of the cylinder. Eight such elongated strip microelectrodeelements 312 are uniformly distributed and wrapped around a 1.27 mmdiameter cylinder. The ends of the microelectrodes may be angular (e.g.,square) or rounded as shown. The dimensions of the elongated stripmicroelectrode elements 312 may range in width from 2 μm or less, to 1mm or larger. They may range in length from 2 μm or less, to 3 mm orlonger.

FIG. 15A through FIG. 15J represent various embodiments ofmicroelectrode arrays. Each of the microelectrode arrays is illustratedin a planar representation. For cylindrical applications, these planarrepresentations would be folded about the cylindrical structure having alongitudinal axis extending vertically with respect to the planarrepresentation, such that the left and right sides of the planarstructure meet along a seam. Also illustrated along the top of eachfigure are reference angular positions varying from 0° to 360°. A firstmicroelectrode array 320 illustrated in FIG. 15A includes a formableplanar substrate 324 including multiple horizontal electricallyconductive stripes 322 a through 322 d (generally 322). When formed in acylindrical fashion, these horizontal stripes represent cylindricalmicroelectrode elements 322. As illustrated, each of the electricallyconductive stripes 322 is located at a respective distance ‘d_(1a)’measured from one of the ends of the formable planar substrate 324 alongthe longitudinal (vertical) axis. Each of the electrically conductivestripes 322 has a respective width ‘w₁’ and center to center spacingwith respect to neighboring conductive stripe 322 of ‘s₁’.

Another embodiment of a microelectrode array 330 is illustrated in FIG.15B. This microelectrode array 330 also includes a number of horizontalelectrically conducting stripes 332. With respect to the stripes 322 ofFIG. 15A, these stripes 332 have a narrower width w₂, a closer center tocenter spacing s₂, and are larger in number. In some embodiments itwould be possible to include electrically conducting stripes having oneor more of various different widths and different spacing. In someembodiments the eight microelectrode strips 332 are connected to eightrespective bond pads (not shown). In yet additional embodiments, theeight microelectrode strips 332 are connected to four bond pads (notshown), resulting in two adjacent strips being in electrical contact.

It is advantageous in at least some instances to treat a target regionwith a probe having a greater number of edges. Edges offer certainadvantages in controlling charge and/or current distributions. To thisend, a microelectrode of a given surface area, can be configured toincrease its perimeter. This can be accomplished, for example, bycontrolling shapes of the microelectrodes. Thus, rather than a simplerectangular arrangement, a microelectrode can have a folded shape (e.g.,a “U” or and “S” or even a comb-like shape). In at least someembodiments, more than one microelectrode are energized by a commonsource (e.g., through a common bonding pad). For example, two or more ofthe microelectrode strips 332 can be connected to the same respectivebond pad. Thus, the eight strips 332 can be controlled through only fourbonding pads.

FIG. 15C illustrates the microelectrode array 350. In the illustrativeexample, the microelectrode array 350 includes four horizontal annularpatterns 356 a through 356 d (generally 356). Each horizontal annularpattern 356 includes a first high-impedance element 356 a, located atapproximately 0° and a second high-impedance element 356 b, located atapproximately 180°. A first low-impedance microelectrode element 358 ais located between the two high-impedance microelectrodes 356 a, 356 b.A second low-impedance microelectrode element 358 b is located to theright of high-impedance microelectrode element 358 b. When formed into acylinder, the two high-impedance microelectrodes 356 a, 356 b opposeeach other, as do the two low-impedance electrodes 358 a, 358 b. In theexemplary embodiment, the annular pattern 352 is repeated at three otherdifferent distances measured with respect to the bottom edge of theformable planar substrate 354. Other embodiments having more or lessannular patterns can be included. Such a configuration is useful forincreasing microelectrode edges in contract with each bonding pad.

Another embodiment of a microelectrode array 340 is illustrated in FIG.15D, similar to that shown in the microelectrode array assembly 260 ofFIG. 11D. This microelectrode array 340 is similar to the microelectrodearray 350 illustrated in FIG. 15C, except that each of the low-impedancemicroelectrode elements have been split into two low-impedancemicroelectrode sub-elements 348 a, 348 b and 348 c, 348 d. In someembodiments the microelectrode sub-elements 348 are electricallyisolated from each other, requiring separate bond pads for each element.In some embodiments, one or more microelectrode stimulation elements 348are electrically connected, requiring only one bond pad to transmit asignal to several elements. Additionally, there are in total sixteenmicroelectrode recording elements 346. In yet another embodiment of amicroelectrode array illustrated in FIG. 15E, each annular pattern 372includes four high-impedance microelectrode elements 376 a through 376 d(generally 376) respectively located at approximately 0°, 90°, 180°, and270°. Each of four relatively low-impedance microelectrode elements 378a through 378 d (generally 378) is located between adjacent pairs ofhigh-impedance microelectrode elements 376. In this embodiment themicroelectrode recording elements 376 are larger and will therefore havedifferent electrical recording characteristics than those demonstratedin FIG. 15D. A planar representation of the microelectrode arrayillustrated in FIG. 14A is shown in FIG. 15F. The microelectrode array360 includes four horizontal annular patterns, each including eightcircular microelectrode 366 elements arranged on a formable planarsubstrate 364.

FIG. 15G illustrates a planar version of the microelectrode array 310shown in FIG. 14B. This microelectrode array 390 includes eightelongated, vertically conducting microelectrode stripes 392 arranged atuniform spacing between 0° and 360° along the formable planar substrate394. FIG. 15H illustrates yet another microelectrode array 380 includingcombinations of the elongated, vertically conducting microelectrodestripes 386 and circular microelectrode elements 384 arranged atrespective longitudinal distances along the formable planar substrate384.

Another microelectrode structure is illustrated in FIG. 15I, having anarrangement similar to that shown in FIG. 15C, in that it includes twoopposing elongated horizontal electrically conducting microelectrodeelements 408 a, 408 b. However, each of the high-impedance contacts 356of FIG. 15C has been replaced by a respective tetrode 406. Each tetrode406 includes an arrangement of four microelectrode elements 410.

Another microelectrode structure is illustrated in FIG. 15J, having anarrangement similar to that shown in FIG. 15A, in that it includeselongated horizontal electrically conducting microelectrode stimulationelements 418 a, 418 b, 418 c. However, between each microelectrode strip418, and above the superior strip 418 a, and below the inferior strip418 c, is an array of microelectrode recording elements 419 a, 419 b,419 c, and 419 d, or generally 419. These microelectrode recordingelements 419 permit recording at different depths in the brain, withrespect to the microelectrode stimulation element 418. In someembodiments, the microelectrode stimulation element 418 is segmentedinto three, or four parts, as demonstrated in FIG. 15D and FIG. 15E. Insome embodiments the microelectrode stimulation elements 418 areelectrically isolated from each other, requiring separate bond pads foreach element. In some embodiments, one or more microelectrodestimulation elements 418 are electrically connected, requiring only onebond pad to transmit a signal to several elements.

FIG. 16A through FIG. 16D and FIGS. 17A and 17B illustrate cutaway viewsof alternative assembly methods for attaching microelectrode films tothe distal ends of neurological probes. These assembly methods can beused for microelectrode films that incorporate microelectronics, or thatdo not incorporate microelectronics. The neurological probes describedherein can be assembled using any one of, or a combination of, thetechniques described in FIG. 16A through FIG. 16D, and FIGS. 17A and17B.

Referring to FIG. 16A, the distal portion of a neurological probe 233,similar to that illustrated in FIG. 4, is shown. The cutaway image isshown in FIG. 16B with part of the microelectrode film 235 removed. Inthis embodiment a cylindrical member 236 contains one or more conductivelead wires 237 along an inner lumen, or alternatively, the lead wireshave been molded in place when the cylindrical member 236 was formed. Inthis embodiment the extension 238 connecting the cylindrically formedouter surface of the microelectrode film 235 is wrapped along the mostdistal portion of the cylindrical member 236. It remains within theinner cylindrical volume formed by the microelectrode film 235. Thedistal portion is covered and sealed using end cap 239 which may beimplemented in a semi-rigid material such as silicone, or a rigidpolymeric or metallic material such as stainless steel. If it isconductive it can also be electrically attached (not shown) to the leadwires 237. Alternatively, end cap 239 can be molded in place, as aglob-top of a polymerizable material such as epoxy or silicone. The leadwires 237 are attached to contact pads 281 thereby electricallyconnecting the proximal portion of the neurological probe to the distalportion.

Referring now to FIG. 16C, the distal portion of a neurological probe243 which is very similar to FIG. 4 is shown. The cutaway image is shownin FIG. 16D with part of the microelectrode film 245 removed. In thisembodiment a cylindrical member 252 contains one or more conductive leadwires 251 along an inner lumen, or alternatively, the lead wires havebeen molded in place when the cylindrical member 252 was formed. In thisembodiment the extension 247 connecting the cylindrically formed outersurface of the microelectrode film 245 is wrapped radially into the mostdistal portion of the cylindrical member 251. It remains within theinner cylindrical volume formed by the microelectrode film 245. Thedistal portion is covered and sealed using end cap 250 which may beimplemented in a semi-rigid material such as silicone, or a rigidpolymeric or metallic material such as stainless steel. If it isconductive it can also be electrically attached (not shown) to the leadwires 251. Alternatively, end cap 250 can be molded in place, as aglob-top of a polymerizable material such as epoxy or silicone. The leadwires 251 are attached to contact pads 282 thereby electricallyconnecting the proximal portion of the neurological probe to the distalportion.

Referring now to FIG. 17A, the distal portion of a neurological probe263 which is very similar to FIG. 4 is shown. The cutaway image is shownin FIG. 17B with part of the entire outer portion of the microelectrodefilm 265 removed. In this embodiment two tubular members constitute theaxis of the neurological probe. A first, outer tubular member 266 isimplemented in a polymeric material such as polyurethane or silicone. Asecond tubular member 267, has an outer diameter less than the innerdiameter of outer tubular member 266, and is implemented in a polymericmaterial such as polyurethane, silicone, or polyimide. Along the spacebetween the two tubular members run one or more conductive lead wires273. Alternatively, the lead wires can be molded in place when the outeror inner tubular member is formed. In this embodiment the extension 275connecting the cylindrically formed outer surface of the microelectrodefilm 265 is wrapped at the most distal portion between the two tubularmembers. The lead wires 273 are attached to contact pads 283 therebyelectrically connecting the proximal portion of the neurological probeto the distal portion.

FIG. 18A illustrates in more detail a proximal portion of the elongatedprobe assembly 420, showing extension of the open ended lumen 424 to theproximal end, terminating in the open end 430. A cross sectional view ofthe four cylindrical contacts 426 is illustrated in FIG. 18B. As shown,each of the elongated helically wound internal electrical conductors 428is connected to a respective one of the four cylindrical contacts 426.Electrical contact can be maintained through bonding, soldering,conductive adhesives, mechanical fasteners, or any combination orsuitable contact means to maintain electrical conductivity between thecylindrical contact 426 and the respective internal electrical conductor428.

FIG. 18C illustrates in more detail a proximal portion of the elongatedprobe assembly 420, in an embodiment where lead wires have been wrappedaxially around an inner tubular structure such as in FIG. 16E. A crosssectional view of the four cylindrical contacts 426 is illustrated. Asshown, each of the elongated helically would internal electricalconductors 429 is connected to a respective one of the four cylindricalcontacts 426. Electrical contact can be maintained through bonding,soldering, conductive adhesives, mechanical fasteners, or anycombination or suitable contact means to maintain electricalconductivity between the cylindrical contact 426 and the respectiveinternal electrical conductor 429.

Referring now to FIG. 19 a cross-sectional view of a portion of ananatomy 748 is shown, illustrating an exemplary microelectrode probeassembly 740 positioned at a neurological target 750. In general, theprobe assembly 740 is representative of an any of the probe assembliesdescribed herein. The microelectrode probe assembly 740 includes anarray of microelectrode elements 742 distributed along an elongatedsupporting structure 744. Preferably, the microelectrode probe assembly740 is shaped and sized to allow one or more of the microelectrodeelements 742 to be positioned at the neurological target 750. To thisend, materials used in construction of microelectrode probe assembly, aswell as one or more of its construction features, size, shape, andorientation can be selected for biocompatibility. As illustrated, one ormore of the microelectrode elements 742 of the microelectrode probeassembly 740 are positioned in intimate contact with the neurologicaltarget 750. One or more additional microelectrode elements 742 of theprobe assembly 740 may reside at locations not in the immediate vicinityof the neurological target 750. In at least some embodiments, one ormore of the microelectrode elements 742 are remotely accessible from aproximal end of the probe assembly 740 via one or more electricallyconductive leads 746.

The supporting structure 744 can be a ridged, or semi ridged structure,such as a an elongated, flat shaft. Alternatively or in addition, thestructure can be a flexible structure, such as one or more flexiblesubstantially non conducting substrate (i.e., a bi-electric ribbon) ontowhich the microelectrode elements 742 are formed as electricallyconductive film layers. The one or more microelectrode elements 742 arein communication with electronic circuitry (not shown) through one ormore electrical leads 746 that can be routed through an internal lumenof a supporting structure 744 and/or formed using elongated film layersalong a flexible, ribbon like supporting structure 744.

In some embodiments, the microelectrode elements 742 can be placed intothe brain generally for recording and/or stimulation of the cortex andfor deep brain stimulation and/or recording of neurological targetsincluding the subthalamic nucleus and the globus pallidus. Themicroelectrode elements 742 can also be placed in other parts of thebody, such as the retina, the peripheral nervous system for neuralrecording and/or neural stimulation of such portions of an animalanatomy. Although microelectrodes are discussed generally throughout thevarious embodiments, there is no intention to limit the upper or lowersize of the microelectrodes. The devices and methods described hereinare generally scalable, with a microelectrode size determined accordingto the attended application. For at least some of the neurologicalapplications, microelectrodes are dimensioned sub-millimeter. In someembodiments, microelectrodes are dimensioned sub-micron. In someembodiments, the microelectrodes are formed as planar structures havinga diameter of about 50 μm that are arranged in a linear array withcenter to center spacing of about 100 μm. The planar structure of themicroelectrodes can have regular shapes, such as circles, ellipses,polygons, irregular shapes, or a combination of such regular and/orirregular shapes.

This probe assembly 740 is implantable near a neurological target, suchas a target brain structure, using common neurosurgical techniques suchas stereotaxis or endoscopy. The device might be inserted withoutsupport or within a cannula which may have an inner dimension slightlylarger than the outer dimension of the device. When used, such a cannulawould be retracted once the device is in position.

The operator can connect the probe assembly 740 to a recorder unitconfigured to identify certain regions of the neurological target (e.g.,the brain) according to the electrical activity. In some embodiments,the microelectrode elements 742 used to record from the neurologicaltarget 750 can be the same microelectrodes as those used to stimulatethe target in application in which both recording and stimulation areaccomplished. Alternatively or in addition, the microelectrodes 742 usedto record from the neurological target 750 can be separatemicroelectrodes 742 from those used to stimulate the target 750. In someembodiments, microelectrodes destined for recording may differ in one ormore of size, shape, number, an arrange from those microelectrodesdestined for stimulation, using different microelectrodes.

The microelectrode elements 742 can be connected to a stimulation sourcethrough one or more interconnecting leads. In some embodiment, at leasta portion of the stimulation source can be extracorporeal. Alternativelyor in addition, the stimulation source can be in vivo. Any implantedelements of the stimulation source are preferably fabricated and/orcontained with a hermetically sealed, bio-compatible envelope. Suchbio-compatible packaging of signal sources is well known, for example,in the area of artificial pacemakers. The stimulation source, whenprovided, may be a controllable signal generator producing a desiredsignal according to a prescribed input. For example, the signalgenerator may receive an input indicative of a desired outputstimulation signal frequency. Such output stimulation signals can have avariety of wave forms, such a pulses, charged balanced pulses,sinusoidal, square wave, triangle wave, and combinations of such basicwave forms.

In some embodiments, the stimulation source includes a pulse generatorfor applying signals to the microelectrodes site. The signals from thepulse generator can be connected directly to the microelectrodes, orthey can be preprocessed using electronics. In some embodiments, suchpreprocessing electronics are embedded within the implantable device.The preprocessing electronics can filter certain parts of an originalsignal, such as a cardiac pacemaker signal, in order to select preferredfrequency components of the original signal that are at or near a peakresistance frequency of the microelectrodes. For embodiments in whichthere are more microelectrodes than signals, electronics can route thestimulation signals to preferred one or more of the microelectrodes.

FIG. 20 is a schematic diagram of one embodiment of a microelectrode tipassembly. The microelectrode tip assembly 500 includes a supportingmember 502 including an elongated portion terminating in a distal tip506 and a somewhat more expansive proximal extension 510. A linear arrayof three microelectrode elements 504 is arranged along a longitudinalaxis of the elongated portion of the support member 502. A correspondingnumber of three electrode contacts 508 are located on the proximalextension 510. Each microelectrode element of the array 504 isinterconnected to a respective one of the electrode contacts 508 througha respective electrically conducting lead trace 512. In the exemplaryembodiment, a polymer layer 514 is applied to at least one surface ofthe underlying support member 502. Each of the microelectrode leads,electrode contacts 508, and interconnecting lead traces 512 isimplemented as an electrically conducting layer on or within the polymerlayer 514. Although a linear array of microelectrode elements is shown,other embodiments are possible with nonlinear, planar, curved surface,and volumetric (i.e., three-dimensional) distributions of suchmicroelectrodes are possible.

FIG. 21 is a schematic diagram of a distal portion of another embodimentof an microelectrode tip assembly 520, including a linear arrangement ofmicroelectrode element arrays 522. Each microelectrode element array 522includes multiple sub-microelectrode elements 524. In the illustrativeembodiments, each of the microelectrode element arrays 522 includes foursub-microelectrode elements 524 arranged in a diamond pattern andreferred to herein as a tetrode. In some embodiment, each of thesub-microelectrode elements 524 is in communication with a respectiveelectrode contact (not shown) through a respective lead trace (notshown). Alternatively or in addition, one or more of thesub-microelectrode elements 524 may share a common lead trace.

The width w′ of the tetrode array 522 is less than a diameter of theelongated support member 525. A height h′ of the tetrode array 522 maybe the same as the width w′ or different, thereby controlling an aspectratio of the tetrode array 522. The center-to-center spacing of adjacenttetrode array elements 522, S′ can be the same, or different measuredalong the length of the array. As shown, each of the sub-microelectrodeelements 524 is identical and circular. In some embodiments, the tetrodeelements 524 are shaped, such as polygons, ellipses, annular rings, andthe like. Alternatively or in addition, one or more of thesub-microelectrode elements 524 of the tetrode array 522 may differ fromother elements of the same array 522. Additionally, tetrode arrayelements 522 may differ in geometry, size, and configuration along thelength of the elongated support member. Once again, two and threedimensional arrangements of such array elements are possible.

Beneficially, the exemplary configuration of sub-microelectrode elementsmay be energized in a variety of different configurations. For example,all four sub-elements 524 may be connected to the same recording orstimulation lead. Alternatively, one or more of the sub-elements 524 maybe coupled to the same recording or stimulation lead (e.g., anode),while one or more of the other sub-elements of the same array 522 may becoupled to a different recording or stimulation lead (e.g., cathode). Insome embodiments, one or more of the sub-microelectrode elements isconnected to an electrical ground.

In some embodiments, each of the sub elements 524 of the exemplarytetrode array 522 is coupled to a respective lead. In recording mode,each sub element 524 is coupled to a respective recording lead. Thus,for each tetrode array 522, the recorder will record four separatechannels Accordingly, electrophysiological activity from the sameneurological target may be recorded independently through each of theindependent sub elements 524 of the tetrode array 522. Dependent atleast in part upon the relative location of the neurological target, thesame electrophysiological activity may be recorded with different timedelays, and perhaps different amplitudes. Using available signalprocessing techniques, the different signals recorded from two or moreof the tetrode sub elements 524 can be further processed to determinerelative location of the neurological target with respect to the tetrodearray 522. Some exemplary techniques available for solving direction tothe target include triangulation and time-difference-of-arrival, inwhich relative delay of the received signals, combined with knowledge ofthe arrangement and spacing of the sub-elements 524 can be used to solvefor distances and/or angles to the target. In use, the tetrode of such atetrode-stimulator hybrid microelectrode would be used to record neuralactivity from a volume of tissue immediately in front of themicroelectrode. The stimulation electrode would be used to stimulateneural activity and transfer charge to that same volume of tissue.

FIG. 22A is a perspective view of one embodiment of an elongatedmicroelectrode assembly 540 having a microelectrode tip assembly 544disposed at a distal end. The exemplary configuration is similar to theneurological probe device 100 illustrated in FIG. 1, except that themicroelectrode array 544 is provided on a distal extension protrudingaway from a distal tip of the assembly 540, rather than being wrappedaround the distal end as shown in FIG. 1. Additionally, there are nomicroelectronic devices included in this assembly 540. Thus,neurological signals, be they detected signals or stimulation signals,are directed along internal wire leads 548 between each of the proximalcontacts 546 and a respective one of the distal microelectrode elements550, shown in more detail in FIG. 22B. The length of the elongatedsupporting cylinder 542 can vary. Also shown in FIG. 22B is a proximalextension 522 including four wire lead contacts 544, each coupled to adistal end of a respective one of the internal wire leads 548. In someembodiments, the microelectrode array 544 incorporates a rigid orsemi-rigid backing.

FIG. 22C is another more detailed view of the distal end of theelongated microelectrode assembly 540 (FIG. 22A). In some embodiments,the rigid tip 544 can be held in place with a biocompatible adhesive560. Alternatively or in addition, at least a distal portion of theelongated supporting cylinder is formed around (e.g., injection molded)a proximal portion of the rigid tip 544. Also apparent in the exemplaryembodiment is the relative arrangement of a support substrate 558 and apolymer layer 514.

FIG. 23 is a perspective view of a distal end of another embodiment ofan elongated microelectrode assembly having an electrode tip assembly564 disposed at its distal end. In particular, the electrode tipassembly 564 includes a microelectronic device 560 mounted thereon. Themicroelectronic device 560 can include an application specificintegrated circuit (ASIC), standard integrated circuits, and othercircuit elements, including resistors, capacitors, inductors, diodes,and transistors. Note that the wires 548 from the contact rings comeinto contact with the electronics. The electronics process the signalsand direct them between one or more remote medical devices and one ormore of the microelectrode sites.

FIG. 24 is a micrograph of a distal portion of an embodiment of amicroelectrode tip 580 including a linear array of eight microelectrodeelements 582. The linear array of microelectrode elements 582 isarranged along a central elongated axis. Distal edges 584 of the deviceare spaced apart from either side the proximal most microelectrode arrayelement and taper towards a distal tip as shown. Placement of theelements apart from the device edge can be beneficial in avoidingunwanted tissue reaction occurring along the edge, the more distalmicroelectrode elements are relatively closer to their adjacent edges584. FIG. 25 is a more detailed micrograph of the distal portion of themicroelectrode tip illustrated in FIG. 24. FIG. 26 is a micrograph of adistal portion of another embodiment of a microelectrode tip 590 inwhich a linear array of microelectrode elements 594 is arranged along aparallel edge 594 of the device 590.

FIG. 27 is a micrograph of a top view of an exemplary arrangement ofconductive elements 601 along an embodiment of a microelectrode array.The device includes a typical microelectrode 601 and trace 603architecture, in which a respective trace interconnecting lead 603 isrouted to each of the microelectrode elements.

FIG. 28A and FIG. 28B are micrograph images of a distal portion of otherembodiments of a microelectrode tip 611, 621.

Fabrication Methods

There are several techniques to achieve the microfabricated componentand the required mechanical and electrical characteristics. Thefabrication procedure is a series of procedural steps in which variouslayers are deposited or removed (e.g., etched) to achieve a final form.Exemplary sequence of procedural steps is described herein.

Step 1: The Carrier Wafer and Sacrificial Layer

In a first step illustrated in FIG. 29A, a carrier substrate 650 isprovided, such as a wafer composed of a crystalline material, such asSilicon, or an amorphous material, such as glass, in particular athermal shock resistant borosilicate glass commercially available underthe brand name PYREX®, or other suitable smooth supportive material. Afirst layer 652 comprising at least two sub-layers is applied to asurface of the wafer 650. One of the sub-layers 652 is a sacrificiallayer deposited on the wafer 650, which will be removed in a subsequentelectrochemical etch step. Preferably, the sacrificial sub-layer ispreceded by another sub-layer, referred to as an underlayer, that willserve to form the electrochemical cell required to etch the sacrificiallayer. In the preferred embodiment, the sacrificial sub-layer isAluminum, or an alloy of Aluminum such as AlSi, which has a smallergranularity, whereas the underlayer is a TiW alloy, Chrome, or similarmetal. The sacrificial layer is represented as a black line 652 in theimage below, the carrier wafer 650 is shown in gray. Each of the imagesillustrated in this series represents a cross section of an exemplaryembodiment, and are used herein to describe the procedural steps.

In some embodiments, the sacrificial layer 652, in addition tofacilitating electrochemical removal of the finished device, is toestablish a granularity, or grain size to the surface of the finisheddevice. Namely, the sacrificial layer can add a micro or nano-roughnessto the surface that can be precisely controlled at least in part by theselection of a suitable underlayer. For example, Aluminum can bedeposited by DC Sputtering with a grain size ranging from 5 nm or lessto 600 nm or more. This grain size provides a first grainy surface. Apolymeric layer is subsequently deposited over the grainy sacrificiallayer. This polymeric layer can be locally etched in order to createvias that open onto the grainy sacrificial layer. Subsequently, a metallayer is deposited over the resulting grainy surface, and polymericlayer, in which the deposited metal serves as theneuro-recording/stimulation microelectrode element, and wire trace. Thearea of the metal that falls into the via in the polymeric layer formsthe microelectrode surface. The area of the metal falls on the polymericlayer can be etched into linear traces and form the interconnect betweenmicroelectrodes and bond pads or circuitry. The process is describedbelow as a “backside microelectrode.” Due to such an increase ingranularity over a relatively flat surface, the overall surface area ofthe metal layer will have a higher effective surface area than that areasubtended by the perimeter of the element. Beneficially, the increasedsurface area results in a corresponding decrease in electrical impedanceof the electrode element. This concept is important in that itfacilitates recording, allowing a greater recording fidelity with lesscomplexity due to the reduction in impedance, while maintaining the samesmall diameter that guarantees high localization of the neural activity.An electrically conducting surface of an exemplary microelectrodeelement thus formed is illustrated in the image of FIG. 30.

Step 2: Deposition of First Polymeric Layer

Referring to FIG. 29B, the next step in the fabrication process includesdepositing a first polymeric layer 654—sometimes referred to as a resinlayer 654. The first polymeric layer 654 can be deposited upon thesacrificial layer 652. This can be done by any suitable means known tothose skilled in the art of MEMS processing, by: (i) spin coating aliquid polymer precursor such as Polyimide or Silicone precursor; (ii)depositing a polymer through chemical vapor deposition as is done withparylene-C; or (iii) laminating a polymer sheet 654 onto the wafer 650.In some embodiments, the polymer layer 654 is heated, or baked, topolymerize.

Referring next to FIG. 29C and FIG. 29D, an optional step includesetching of first polymeric layer 654, as may be beneficial whenpreparing a device having one or more backside electrodes, that willultimately be located along an underside of the finished device. In thisoptional step, the first polymeric layer 654 is locally etched in orderto form open areas 652, where metals for such backside microelectrodesmay be later deposited. This step is optional, and unnecessary whenthere is no need for any such backside electrodes on the finisheddevice—all microelectrode contacts being formed on a front surface ofthe finished device. This step is also advantageous, because thebackside electrode metal layer, when included, will also benefit fromthe higher effective surface area that can be gained from thesacrificial layer's granularity.

The etching can be performed by depositing a mask 656 on the firstpolymeric layer 654. Using well established methods for thin filmprocessing, the mask 656 can be photolitho-graphically defined. Forexample, a photosensitive resin 656 is spin coated onto the polymericlayer 654. A process of exposing an unmasked portion of the resin layer657 to UV light is used for those areas in which the operator chooses toremove the polymer layer 654. The device is developed in a solvent thatwill selectively remove only the unmasked areas 657 that were exposed toUV light. This selective etching process locally opens areas of thepolymeric layer 654, by etching, exposing in this instance theunderlayer 652. In some embodiments the device is etched in oxygenplasma to remove the exposed portion of the polymeric layer 657. Theetch mask 656 may also be removed by the same etching process, but if itis thicker than the polymer layer it may not be completely removed.Illustrated in the figures is a defined etch mask 656. Alternatively orin addition, the etch mask 656 can also be implemented in anon-photodefinable layer, such as Silicon Dioxide deposited by DCSputtering. The Silicon Dioxide then has the photoresist deposited andphotolithographically defined on top of it. After etching the polymericlayer 654, the Silicon Dioxide mask can be optionally removed.

FIG. 29D illustrates the device after the exposed portion of the polymerlayer 657 was removed. As illustrated, a portion of the sacrificiallayer 652 is now exposed. In some embodiments, the photoresist mask 656cab be subsequently removed using a suitable solvent.

Step 3: Deposition and Definition of Metal Layer

The deposition of the layer can also be made through a resist mask 670,as shown in FIG. 29G. In this case a photoresist mask 686′ would bephotolithographically defined on the polymer layer 654. An electricallyconductive (e.g., metal) layer 692′ can then be deposited over themasked device. Thus, unmasked areas 687 at which it is desirable to havean electrically conducting layer 690 formed, are open with respect tothe photoresist mask 686′, such that the a portion of the depositedelectrically conductive layer 692′ lands directly onto the polymericlayer 654 at the unmasked area 687. This technique is sometimes referredto as a “lift off” technique. The photoresist mask 686′, with anyelectrically conductive layer 692′ thereon, is then dissolved, such thatthe only remaining metal 690 is on the polymer at the formerly unmaskedareas. Note that the metal layer 692′ on top of the photoresist 686′ isalso removed by removal of the photoresist mask 686′. Beneficially, thatportion of the electrically conducting layer 690 in contact with thepolymeric layer 654 remains after removal of the mask 686′.

In an alternative method, referring now to FIG. 29H, a metal layer 692″can be deposited onto the entire surface of a wafer 650. As illustrated,the metal layer 692″ is provided on top of the polymeric layer 654,which is provided on top of the sacrificial layer 652. A masking layer686″ is provided over that portion of the metal layer 692″ to remain.Exposed regions of the metal layer 692″ can then be removed locally by aphotolithographic step such as demonstrated below.

Referring next to FIG. 29E, an electrically conductive layer that servesas the electrode 680 and one or more electrically conductive traces 682is next deposited. Such an electrically conductive layer can include ametal layer deposited by any suitable thin-film process, such as DCsputtering, RF Sputtering, or evaporation techniques. The metaldeposited in the electrically conductive layer 680, 682 is preferablyplatinum, iridium, platinum-iridium alloy, iridium-oxide, titanium, or atitanium alloy to ensure acceptable electrical characteristics (such ascharge transfer) and mechanical strength.

In a preferred embodiment the metal layer 680, 682 is deposited with anadhesion promotion layer in contact with the polymer. For example,titanium can be sputtered onto the polyimide layer 654 in an initialpartial step to improve adhesion, followed by a platinum layer depositedin an intermediate partial step, and optionally, a titanium layer maythem be deposited onto the platinum layer in a subsequent partial step.This creates a Ti—Pt—Ti sandwich, where the titanium is responsible foradhering the platinum to the polyimide on either side of it, and theplatinum is the metal layer that will be used.

For embodiments that produce backside electrodes, as described above inreference to FIG. 29C through FIG. 29E, then the electrically conductivelayer 680 will be in contact with the sacrificial layer 652 in theregion of the backside electrode 680. The metal deposition technique isselected to ensure that there is contact between the metal on top of thepolymeric layer 654, and the metal on the exposed portion of thesacrificial layer 652. This is done by ensuring the metal 680 isconformally deposited, and that the polymeric layer 654 is not toothick. The metal layer 680 can then be photolithographically defined asexplained above. An etch in a plasma, such as Chlorine gas plasma, canbe used to remove the metal layers deposited using a photoresist mask.The photoresist mask can then be removed in a solvent.

Step 4: Deposition of 2nd Polymeric Layer

Referring next to FIG. 29I for a backside electrode embodiment and FIG.29H, a second polymeric layer 672, 692 is deposited using a suitabletechnique, such as any of the techniques described above with respect toFIG. 29B. The second polymeric layer 672, 692 is deposited onto theunderlying polymeric layer 654, 664, and any exposed metal layer 658,668. In some embodiments, the first polymeric layer 654, 664 can beprocessed in order to increase its adhesion to the second polymericlayer 672, 692. For example, such processing can be accomplished throughsurface roughening or chemical alteration using an oxygen plasma. Thesecond insulative, or polymeric layer 672, 692 isolates the electricaltraces, when formed on different layers with respect to each other. Insome embodiments, the polymeric material can be subjected to thermalprocess, such as baking.

Step 5: Definition of Polymeric Layers

Referring next to FIG. 29I through FIG. 29K, to define the one or morepolymer layers 654, 691 and therefore the device itself, an etch mask695 is deposited to an external surface of the device. This etch mask695 may consist of a photodefinable resist but preferably it will be ahard etch mask such as silicon dioxide or amorphous silicon which canwithstand the etch of the polymeric layer without significantdegradation.

The wafer 650 at this point also has a hard mask 693 deposited, forexample, by DC or RF sputtering. A photodefinable 695 resist isdeposited on the hard mask 693 and the areas of the polymer 654, 691that are to be etched are defined.

The hard mask 693 is then etched with a different gas then would be usedto etch the polymeric layer 654, 691, for example CF4 plasma. Now theone or more polymeric layer 654, 691 can be etched with a gas, such asoxygen plasma, to the sacrificial layer 652, as shown. Thus, theremaining portions of the hard mask shown in FIG. 29K define the extentof the device, by defining the device's edges 659.

The remaining portions of the hard mask 693 can be optionally removed ina subsequent step. The goal of this etching process is to: (i) definethe microelectrode sites; (ii) define the device shape; and (iii) definethe contact areas for electronics or wire attachment. A top view of anexemplary finished microelectrode device is shown in FIG. 31D. Across-section of another exemplary finished microelectrode device isshown in FIG. 32A.

If the option of making backside electrodes is taken in step 2, thedevice will have microelectrodes at its surface once removed from thesubstrate. Such a device is shown in FIG. 24 and FIG. 25. Exemplaryfront side electrodes are shown in the device of FIG. 28B.

Step 6: Optional Bonding of Electronics

If the device is to be integrated with electronics, referring now toFIG. 29L, the contact pads 699 can be used at this point to connect toan electrical circuit device 697. For example, an Integrated Circuitchip 697 can be connected to the contacts 690 (FIG. 29K) by flip-chipbonding the chip 697 to the device 661, using a conductive epoxyinterlayer. The chip 697 can then be further attached by chemicalbonding, such as an epoxy to ensure a strong and reliable connection tothe device 661.

Step 7: Removal of Devices from Carrier Wafer

A final step of the fabrication process is illustrated in FIG. 29M, toremove the device 661, such as a MEMS device, from the underlying wafer650. The sacrificial layer 652 (e.g., FIG. 29L) is electrochemicallyetched away. Removal of the sacrificial layer 652 from under the device661, frees the underside of the device 661 from the wafer 650. This canbe accomplished by placing the wafer in a saline bath with a high NaClconcentration. A platinum electrode in the bath can be used as areference. A voltage is applied to the aluminum layer with respect tothe platinum electrode. The electrochemical cell created by the Aluminumand TiW etches the aluminum, and this etch continues below the devices.The devices fall into the bath and are removed.

FIG. 30 is a micrograph of an embodiment of a backside microelectrodeelement 700. The image is taken at the process step shown in FIG. 29E.The granularity 702 of the aluminum sacrificial layer surface 704 isused to increase the effective surface area of a metal electrode in asubsequent step. Also shown is a portion of an interconnecting lead 706in electrical communication with the microelectrode element 700.

FIG. 31A is a planar view of a construction element of an embodiment ofa microelectrode tip. The construction element includes a stencil frametree 640 including eight rigid backing members 642 releasably attachedto a supporting construction frame 644. Each of the rigid backingmembers 642 includes an elongated portion, and an proximal portionhaving an opening 646 to accommodate one or more electronic devices,when fabricated. The stencil frame tree 640 can be implemented in arigid material, such that each of the individual supporting constructionframes can be bonded to the devices on the carrier wafer.

FIG. 31C illustrates an exploded schematic view of a constructionelement of an embodiment of a microelectrode array tip. The stencilframe tree 400 is placed on a surface of a carrier wafer includingmicro-array devices 649 formed therein. The stencil frame tree 400 issuitably aligned with the micro-array devices 649 of the carrier wafer648, and bonded thereto. One or more electronic devices can be suitablyplaced on the polymer devices either after or before the stencil frametree 400 is bonded to the carrier wafer 648.

FIG. 31B is a schematic view of a portion of the construction elementillustrated in FIG. 31C, illustrating a close up of the assembledcomponents. In this exemplary embodiment, the polymer devices werefabricated using a “backside” electrodes process.

FIG. 31D is a schematic view of another portion of the constructionelement illustrated in FIG. 31B. Once the sacrificial layer has beenremoved as described above in relation to FIG. 29, the devices 649 arereleased from the carrier wafer 648 and are now bonded to the stencil640 for support. In the exemplary embodiment, the side of the polymericdevice 649 facing the carrier wafer 648 (and in contact with thesacrificial layer) has the microelectrodes at its surface. In general,microelectrodes may be included in either or both sides as describedherein.

In some embodiments, a rigid back 642 (FIG. 31A) on the polymermicro-device 649 is required. This renders the device 649 fully, orlocally, rigid. This rigidity might be advantageous for insertion intotissue. The concept is a stencil shape 640 which can be bonded onto thedevices on the carrier wafer where they have been fabricated. Thestencil shape 640 can be implemented in a polymer, such as PEEK orPolyurethane, or in metal such as Medical Grade Stainless Steel orTitanium. It can be molded into shape, cut by machining or laser, orstamped out. When this rigid structure has been attached to the devices,the electronic chip can be bonded. The electronic chip can also bebonded to the devices beforehand. After the assembly process the devicescan be removed from the carrier wafer using the same sacrificial etchingtechniques as described above. A further assembly procedure can be toremove the rigid backing from its frame and integrate the device withits final structure. In some embodiments, the rigid backing isconductive. In other embodiments, the rigid backing is non-conductive.When this support structure is of a conductive material, it can alsoserve as the electrical ground or reference for the stimulation.

Electronic Components

The electronic components of the device enable: (i) recording of neuralactivity from the microelectrode array to identify which microelectrodesites are closest to the stimulation region of interest; and (ii)stimulation and modulation of neuronal activity with the microelectrodearray and the ability to select which microelectrode sites stimulating.

The electronics can be implemented using discrete components, integratedcircuit technology, or a combination of both. A black box design of theelectronics is shown below. The electronics can be driven by an existingImplantable Pulse Generator (IPG), but will include a telemetricprogramming interface to properly condition or route the signal from theIPG to the microelectrode array. An embodiment of the electroniccomponents exists which does not require the IPG.

Mechanical Components

The mechanical components and associated assembly processes serve tohouse the device in a hermetic and biocompatible manner. They alsoenable connection to an existing Implantable Pulse Generator or theextra-corporeal control unit. The extra-corporeal unit provides power,programming ability and retrieval of information. It can be implantedmuch like the external cochlear stimulation systems that exist today. Inan embodiment that includes an Implantable Pulse Generator, it wouldserve to retrieve information and program the electrical unit to routethe signals from the IPG to the microelectrode array.

Referring to FIG. 33, a functional block diagram of an exemplaryembodiment of a neurological target stimulator 820 configured in astimulation mode. The stimulator 820 includes an implantable portion 822including a microelectrode array 826 positionable at a neurologicaltarget. The implantable portion 822 also includes a signal generationdevice 828 for actively stimulating the neurological target. In someembodiments, each of the one or more microelectrodes of themicroelectrode array 826 is in communication with a dedicated signalgeneration device 828. The respective stimulation signal provided at anoptimized frequency for each individual microelectrode-tissue interface,based on a peak resistance frequency. The implantable portion 822 caninclude a power source 832, such as a battery. In some embodiments, theimplantable portion 822 also includes a telemetry and control module 834configured for external communication with an extra-corporeal unit 824.Such a feature can be used to provide extra-corporeal control foroperating the implantable portion 822.

Referring to FIG. 33, a functional block diagram of another exemplaryembodiment of a neurological target stimulator 840 is illustratedconfigured in so-called routing mode. The stimulator 840 includes animplantable portion 842 including a microelectrode array 846positionable at a neurological target. The implantable portion 842 alsoincludes a signal routing circuit 850 configured to direct a stimulationsignal to one or more of the microelectrodes 846 for activelystimulating the neurological target. In this embodiment, the stimulationsignal is obtained from a separate, implantable pulse generator 857. Thepulse generator 857 is in communication with the implantable portion 842through an interconnection cable 856 containing one or more signalleads. The implantable portion 842 also includes at least one signalconditioner 848 configured to condition an output signal from the pulsegenerator 857 suitable for stimulation of the neurological targetthrough one or more of the microelectrodes 846. The implantable portion232 generally includes a power source 852, such as a battery. In someembodiments, the implantable portion 842 also includes a telemetry andcontrol module 854 configured to communicate with an extra-corporealunit 844, to provide controls for operating the implantable portion 842.

Filtering of an Existing Signal

In some embodiments, the signal conditioner 848 include a filteringcircuit to pre-filter or gain adjust (e.g., pre-amplify and/orattenuate) or otherwise condition an existing signal before routing itto a microelectrode array. Several popular filter options includedigital filters, such as infinite impulse response (IIR) filters,electronic filters using one or more electrical components, such asinductors and capacitors, and surface acoustic wave (SAW) devices. Thefilters can be designed through well known filter synthesis techniquesto have a preferred performance features. Some of the controllablefeatures in filter synthesis include filtration bandwidth, cornerfrequency, pass-band ripple, and relative sideband level. Such filtersinclude categories referred to as Butterworth, Chebyshev 1 and 2, andElliptic filters. The particular implementation—whether analog ordigital, passive or active, makes little difference as the output fromany implementation would still match the desired output.

FIG. 35 is a functional block diagram of another embodiment of aneurological microelectrode target stimulator 814 is shown. Thestimulator 814 includes a microelectrode array 815 positionable at aneurological target of interest. The stimulator 814 also includes animpedance analyzer 816 configured for measuring an electrical impedance,a preferred frequency detector 817, and a stimulator 818 forelectrically stimulating the neurological target.

The impedance analyzer 816 can use any of various known techniques formeasuring electrical impedance. Generally, the impedance analyzer 816provides a test electrical signal having known or measurable attributesto the microelectrode-tissue interface. Such attributes include avoltage level of a voltage source, or a current level of a currentsource. The test voltage or current, as the case may be, when applied tothe microelectrode-tissue interface, induces a sensed current or voltageaccording to physical properties of the microelectrode-tissue interface.The impedance analyzer 816 can form a ratio of the test signal to thesensed signal, yielding an impedance value according to Ohm's Law:Z=V/I. As the microelectrode-tissue impedance Z is a complex quantity,each of the test and sensed electrical signals is identified as havingboth a magnitude and a phase.

In operation, the impedance analyzer measures a complex impedance of themicroelectrode-tissue interface surrounding the at least onemicroelectrode 815. The impedance analyzer repeats the measurements atmultiple different frequencies, by varying frequency of the applied testelectrical signal. Preferably, the multiple frequencies span a frequencyrange that includes biologically relevant frequencies. The preferredfrequency detector 817 identifies the measured impedance being closestto a pure resistance. Such a determination can be accomplished byidentifying the measured impedance value having a phase value closest tozero. For example, a measured impedance can be identified having minimumabsolute value phase (i.e., MIN|<Z|). Such a determination can also beaccomplished by identifying the measured impedance value having aminimum reactance (i.e., MIN(Im{Z})). The frequency at which theimpedance determined to be closest to a pure resistance is identified asa preferred stimulation frequency. The stimulator 818 is then adjustedto provide a stimulation signal at a frequency, or frequency band, at ornear the preferred stimulation frequency. The stimulation signal is thenapplied to the microelectrode array 815.

A top view of an exemplary embodiment of a microelectrode assembly 920is illustrated in FIG. 36. The assembly 920 includes an array ofmicroelectrodes 922 positioned along a distal end of an elongated probesubstrate 924. A first electronic assembly 928 is positioned at aproximal end of the elongated probe substrate 924. The first electronicassembly 928 can include one or more integrated circuit elements 921,such as a microprocessor, and one or more discrete electronic components932. The first electronic assembly 928 is interconnected to each of themicroelectrodes 922 through a respective trace 926 running along theelongated probe substrate 924. The electronic assembly 928 and can beconfigured to implement one or more functions of the implantableneurological stimulator described herein. In some embodiments, theelongated probe substrate also includes at least a portion of theelectronic assembly 928.

In some embodiments, the first electronic circuitry 928 is connected toan implanted pulse generator (not shown) through a cable 924. In someembodiments, as shown, a second electronics assembly (or a portion ofthe first electronics assembly) includes telemetry circuitry 939, suchas a telemetry antenna. In the exemplary embodiment, at least a portionof electronic circuitry 928, 938 is positioned adjacent to themicroelectrodes 922, for example being joined by the elongated probesubstrate 924.

The mechanical components and associated assembly processes serve tohouse the assembly 920 in a hermetic and biocompatible manner. They mayalso enable connection to an existing Implantable Pulse Generator or theextra-corporeal control unit. The extra-corporeal unit can providepower, programming ability, and retrieval of information. In someembodiments, the assembly 920 can be implanted much like currentlyavailable external cochlear stimulation systems. In an embodiment thatincludes an implantable pulse generator, it would serve to retrieveinformation and program the electrical unit to route the signals fromthe implantable pulse generator to the microelectrode array 922.

The device provides highly localized and efficient stimulation byincorporating microfabricated components, electronic components andmechanical components. The microfabricated component consists of amicroelectrode array. This array can be implemented in a polymericmaterial such as polyimide, polyurethane, parylene, or polysiloxane(silicone) and includes thin film or plated layers of a metal or metaloxide with high charge transfer capability such as platinum,platinum-iridium, iridium, iridium oxide or titanium. The polymeric andmetallic layers can be deposited sequentially and formed usingestablished principles of microfabrication such as spin coating, DC/RFsputtering, photolithography, plasma etching, and etching with a maskconsisting of a secondary or sacrificial material such as silicondioxide or photosensitive resist. The metallic layer can be formed tocreate the microelectrode arrays and traces which connect the array tothe electronics and housing. The polymeric layers serve to isolate thetraces from each other but also provide the structure of the implant'sstimulating/recording tip. There are several fabrication methods whichcan be described to build such a microfabricated component.

The electronic or microelectronic components of the device enable: (i)the ability to identify the peak resistance frequency for eachindividual microelectrode site using electrical impedance spectroscopy;(ii) stimulate at the characteristic peak resistance frequency of eachmicroelectrode (this guarantees minimized signal distortion and maximumcharge transfer to the tissue); and (iii) stimulation and modulation ofneuronal activity with the microelectrode array and the ability toselect which microelectrode sites are stimulating.

The electronics can be implemented using discrete components, integratedcircuit technology, digital signal processing (DSP), or a combination ofall three. The electronics can be incorporated in one unit, or can beused in conjunction with an existing implantable pulse generator (IPG).The electronics may include a telemetric programming interface toproperly condition or route the signal from the IPG to themicroelectrode array.

Referring to FIG. 37, a side view of an exemplary alternative embodimentof a microelectrode structure is illustrated. In this embodiment, anelectronics assembly 956 is positioned remote from the microelectrodearray 952. The microelectrode array 952 is joined to the electronicsassembly 956 through an arrangement of interconnecting electrical leads954. The electronics assembly 956 can be configured to implement one ormore functions of the implantable neurological stimulator describedherein. As illustrated, the electronics assembly 956 can also beconnected to an implanted pulse generator (not shown) through aninterconnecting cable 960. Alternatively or in addition, the electronicsassembly 956 can include telemetry circuitry for communicating with anexternal telemetry device 962.

The electronics assembly can include an electrical grounding lead forinterconnection to an electrical ground potential 958. In any of theembodiments described herein, impedance measurements and/or stimulationcan be implemented between two or more microelectrodes (e.g., adjacentmicroelectrodes). Alternatively or in addition, impedance measurementsand/or stimulation can be implemented between one or moremicroelectrodes and an electrical ground reference.

Note that a device can be assembled to not include electronics. Thisdevice would then transfer the signal from the Implantable PulseGenerator directly to the electrodes. A device with electronics wouldfirst “pre-filter” the signal before applying to the electronics. This“pre-filter” might take the form of signal filtering in order to achievea certain signal spectrum, multiplexing and routing in order to directsignals from a pulse generator to a choice of microelectrode sites. Thefollowing figures demonstrate the different components and embodiments.

Various exemplary embodiments of microelectrode array elementconfigurations including tetrode arrangements are illustrated in FIG.38A through FIG. 38D. Referring to FIG. 38A, a microelectrode arrayelement 1000 includes a stimulation electrode 1002 and four recordingelectrodes 1004. In the exemplary embodiment, the stimulation electrode1002 is disc-shaped; however, other shapes are anticipated, such aspolygons, ovals, and irregular shapes. In this embodiment, the recordingelectrodes 1004 are substantially smaller than the stimulation electrode1002, and positioned within the outer perimeter of the stimulationelectrode 1002. In order to accommodate this arrangement, thestimulation electrode includes a respective open area 1006, one for eachof the recording electrodes. In the exemplary embodiment, the recordingelectrodes 1004 are uniformly spaced having about 90° angular separationbetween adjacent pairs.

In general, the open areas 1006 can have any shape, and the shape neednot be the same as the shape of any recording electrode 1004 that may bepositioned therein. In the exemplary embodiments, the open areas 1006 dohave a similar shape, namely a circle, as the disc-shaped recordingelectrodes 1004. The openings are dimensioned larger than the recordingelectrodes 1004, such that the recording electrodes can be placed withinthe open areas 1006, without touching the stimulation electrode 1002. Anannular region of separation exists between the two electrodes 1002,1004. The recording electrodes 1004 may each be similarly shaped and/orsimilarly sized with respect to each other. They may have similar shapeas the stimulation electrode 1002, or have a different shape. In someembodiments, at least some of the recording electrodes 1004 havedifferent shapes and/or different sizes with respect to each other.

In the exemplary embodiment, the four disc electrodes 1004 embeddedwithin the larger, stimulation electrode 1002. The recording electrodes1004 each have a respective diameter of about 50 μm, and a relativeseparation to their nearest neighbors of about 150 μm. The stimulationelectrode has a diameter of 300 μm. In some embodiments, the diameter ofeach recording electrode can range between about 2 μm or less, and about300 μm or more. In some embodiments, the diameter of the stimulationelectrode can range between about 5 μm or less, and about 1,000 μm ormore.

Referring to FIG. 38B, an alternative embodiment of a microelectrodearray element 1010 shows a stimulation electrode 1012 as a non-closeddisc. The outer perimeter of the stimulation electrode 1012 generallyfollows a circular arc, with indentations defining open areas 1016extending in from the perimeter, towards the center of the electrode1012. In particular, four such open areas 1016, or slots, eachaccommodate a respective recording electrode 1014. The recordingelectrode 1014 is positioned toward an inner end of the open area 1016,nearest the center of the stimulation electrode 1012. In at least someembodiments, the recording electrode 1014 is spaced apart from aperimeter of the open area 1016, such that the recording electrode 1014does not touch the stimulation electrode 1012. In some embodiments, theperimeter of the stimulation electrode 1012 are generally rounded,without sharp corners, in order to prevent highly localized fields.Although a four-recording electrode embodiment is shown, otherembodiments are possible including one or more recording electrodespositioned within respective open areas 1016. Although circular shapesare illustrated for each of the stimulation electrode and the recordingelectrode, different shapes can be used. The shapes can be regular, suchas ellipses, polygons, and irregular shapes.

Referring to FIG. 38C, illustrates a similar embodiment of amicroelectrode array element 1020 to that described above, except thattwo tetrodes 1024 a, and 1024 b are embedded within the same stimulationelectrode 1022. The two tetrodes 1024 a, 1024 b can record neuralactivity from different tissue volumes sizes, with differentsensitivities to neural activity. The “inner tetrode” 1024 b can havethe same, or different microelectrode diameters than the “outer tetrode”1024 a. The diagram shows an “inner tetrode” with 50 μm discs, and an“outer tetrode” with 60 μm discs. Other shapes, sizes, and numbers oftetrode elements are possible.

Referring to another microelectrode element embodiment 1030 illustratedin FIG. 38D, a tetrode 1034 is only slightly embedded into thestimulation electrode 1032. As shown, the innermost portion of the openarea 1036 is spaced apart from an outer perimeter of the stimulationelectrode 1032 by a distance less than a diameter of the recordingelement 1034. Such a configuration would allow adjustment andoptimization of the sensitivity and volume of tissue being recorded.

Various embodiments of neurological stimulation devices and techniqueshave been described herein. These embodiments are given by way ofexample and are not intended to limit the scope of the presentinvention. It should be appreciated, moreover, that the various featuresof the embodiments that have been described may be combined in variousways to produce numerous additional embodiments.

One or more of any of the microelectrode array elements 1000, 1010,1020, 1030 described above can be positioned on an elongated cylindricalmember, forming a microelectrode array. Alternatively or in addition,one or more of any of the microelectrode array elements 1000, 1010,1020, 1030 described above can be positioned on an elongated planarmember, also forming a microelectrode array. An exemplary planar probeextension 1040 is illustrated in FIG. 39A. The probe extension 1040includes four microelectrode elements 1045. Each of the microelectrodeelements 1045 includes a respective stimulation electrode 1042 andtetrode arrangement of recording electrodes 1044. In the illustrativeembodiment, discoid tetrode elements 1044 are disposed along an externalperimeter of a discoid stimulation electrode 1042, such that the tetrodeelements 1044 are spaced apart from the outer perimeter of thestimulation electrode 1042.

Another alternative embodiment of a planar probe extension 1050 isillustrated in FIG. 39 In this embodiment, each of the a probe extension1050 includes four microelectrode elements 1055. Each of themicroelectrode elements 1055 includes a respective stimulation electrode1052 and tetrode arrangement of recording electrodes 1054. In theillustrative embodiment, discoid tetrode elements 1054 are disposedwithin an open interior region of an annular stimulation electrode 1052,such that the tetrode elements 1054 are spaced apart from the innerannular perimeter of the stimulation electrode 1052.

Various embodiments of micro-fabricated neurostimulation devices havebeen described herein. These embodiments are giving by way of exampleand are not intended to limit the scope of the present invention. Itshould be appreciated, moreover, that the various features of theembodiments that have been described may be combined in various ways toproduce numerous additional embodiments. Moreover, while variousmaterials, dimensions, shapes, implantation locations, etc. have beendescribed for use with disclosed embodiments, others besides thosedisclosed may be utilized without exceeding the scope of the invention.

Although some devices described herein are identified as eithercutaneous or chronic, it is understood that such cutaneous devices maybe used in chronically, being implanted for extended periods, or evenindefinitely. Similarly, any devices described herein as being chronic,it is understood that such devices may also be used cutaneously.

While this invention has been particularly shown and described withreferences to preferred embodiments thereof, it will be understood bythose skilled in the art that various changes in form and details may bemade therein without departing from the scope of the inventionencompassed by the appended claims.

What is claimed:
 1. An implantable neurological device, comprising: asupport tube; a cylindrical member coupled with the support tube, thecylindrical member comprising a distal end, a proximal end, and aninternal lumen, a plurality of circumferential, segmented electrodesspaced along a longitudinal axis of the cylindrical member, each of theplurality of circumferential, segmented electrodes comprising at leastthree microelectrodes arranged along the longitudinal axis; and alongitudinal extension having at least a portion extending in theinternal lumen of the cylindrical member.
 2. The device of claim 1,comprising: an electrically conductive layer having at least oneinterconnecting lead trace and at least one electrode contact toelectrically couple with the plurality of circumferential, segmentedelectrodes.
 3. The device of claim 1, further comprising: anelectrically insulative layer applied to the support tube, theelectrically insulative layer including an electrically conductive layerto electrically couple with the plurality of circumferential, segmentedelectrodes.
 4. The device of claim 1, further comprising: an electricalcomponent electrically coupled among the plurality of circumferential,segmented electrodes and a plurality of electrode contacts disposed onthe longitudinal extension.
 5. The device of claim 1, furthercomprising: at least one circumferential electrode of the plurality ofcircumferential, segmented electrodes disposed about the longitudinalaxis of the cylindrical member.
 6. The device of claim 1, furthercomprising at least one of the at least three microelectrodes in each ofthe plurality of circumferential segmented electrodes electricallycoupled with the internal lumen via an electrical lead.
 7. The device ofclaim 1, further comprising at least one of the at least threemicroelectrodes in each of the plurality of circumferential, segmentedelectrodes having a recording element to acquire a measurement signalabout a neurological target.
 8. The device of claim 1, furthercomprising at least one of the at least three microelectrodes in each ofthe plurality of circumferential, segmented electrodes having astimulating element to apply stimulation to a neurological target. 9.The device of claim 1, further comprising each microelectrode of the atleast three microelectrodes in each of the plurality of circumferential,segmented electrodes having a shape, a size, and an orientation definedbased on a neurological target of the microelectrode.
 10. The device ofclaim 1, further comprising: at least three microelectrodes of each ofthe plurality of circumferential, segmented electrodes located along thelongitudinal axis in at least one of a linear distribution, a non-lineardistribution, a planar distribution, a curved distribution, and avolumetric distribution.
 11. The device of claim 1, further comprising:each microelectrode of the at least three microelectrodes configured tobe independently addressable to provide simulation via themicroelectrode.
 12. The device of claim 1, further comprising: aformable planar substrate to accommodate the plurality ofcircumferential, segmented electrodes, each of the least threemicroelectrodes secured in at least a portion of the formable planarsubstrate.
 13. The device of claim 1, further comprising: amicroelectrode film coupled with an outer surface of the cylindricalmember, the microelectrode film comprising the plurality ofcircumferential, segmented electrodes and the longitudinal extension,the longitudinal extension extending from a distal end of themicroelectrode film.
 14. A method of implanting of neurological devices,comprising: implanting a neurological device, comprising: a supporttube; a cylindrical member coupled with the support tube, thecylindrical member comprising a distal end, a proximal end, and aninternal lumen, a plurality of circumferential, segmented electrodesspaced along a longitudinal axis of the cylindrical member, each of theplurality of circumferential, segmented electrodes comprising at leastthree microelectrodes at a common location along the longitudinal axis;and a longitudinal extension having at least a portion extending in theinternal lumen of the cylindrical member.
 15. The method of claim 14,wherein the neurological device further comprises an electricallyconductive layer having at least one interconnecting lead trace and atleast one electrode contact to electrically couple with the plurality ofcircumferential, segmented electrodes.
 16. The method of claim 14,wherein the neurological device further comprises each microelectrode ofthe at least three microelectrodes in each of the plurality ofcircumferential, segmented electrodes having a shape, a size, and anorientation defined based on a neurological target of themicroelectrode.
 17. The method of claim 14, wherein the neurologicaldevice further comprises at least three microelectrodes of each of theplurality of circumferential, segmented electrodes located along thelongitudinal axis in at least one of a linear distribution, a non-lineardistribution, a planar distribution, a curved distribution, and avolumetric distribution.
 18. The method of claim 14, wherein theneurological device further comprises a microelectrode film coupled withan outer surface of the cylindrical member, the microelectrode filmcomprising the plurality of circumferential, segmented electrodes andthe longitudinal extension, the longitudinal extension extending from adistal end of the microelectrode film.
 19. The method of claim 14,further comprising: supplying an electrical signal to the plurality ofcircumferential, segmented electrodes of the neurological device tostimulate a neurological target.
 20. The method of claim 14, furthercomprising: recording a measurement signal from the plurality ofcircumferential, segmented electrodes of the neurological device.